EP2845569A1 - Système d'administration pour implant vasculaire - Google Patents

Système d'administration pour implant vasculaire Download PDF

Info

Publication number
EP2845569A1
EP2845569A1 EP14193715.1A EP14193715A EP2845569A1 EP 2845569 A1 EP2845569 A1 EP 2845569A1 EP 14193715 A EP14193715 A EP 14193715A EP 2845569 A1 EP2845569 A1 EP 2845569A1
Authority
EP
European Patent Office
Prior art keywords
implant
proximal
distal
mount
delivery device
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP14193715.1A
Other languages
German (de)
English (en)
Inventor
Arshad Quadri
J. Brent Ratz
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cardiaq Valve Technologies Inc
Original Assignee
Cardiaq Valve Technologies Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=41328427&utm_source=***_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP2845569(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Cardiaq Valve Technologies Inc filed Critical Cardiaq Valve Technologies Inc
Publication of EP2845569A1 publication Critical patent/EP2845569A1/fr
Withdrawn legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2442—Annuloplasty rings or inserts for correcting the valve shape; Implants for improving the function of a native heart valve
    • A61F2/246—Devices for obstructing a leak through a native valve in a closed condition
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
    • A61F2/2418—Scaffolds therefor, e.g. support stents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2427—Devices for manipulating or deploying heart valves during implantation
    • A61F2/243—Deployment by mechanical expansion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2427—Devices for manipulating or deploying heart valves during implantation
    • A61F2/2439—Expansion controlled by filaments
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/9517—Instruments specially adapted for placement or removal of stents or stent-grafts handle assemblies therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2002/9505—Instruments specially adapted for placement or removal of stents or stent-grafts having retaining means other than an outer sleeve, e.g. male-female connector between stent and instrument
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2002/9505—Instruments specially adapted for placement or removal of stents or stent-grafts having retaining means other than an outer sleeve, e.g. male-female connector between stent and instrument
    • A61F2002/9511—Instruments specially adapted for placement or removal of stents or stent-grafts having retaining means other than an outer sleeve, e.g. male-female connector between stent and instrument the retaining means being filaments or wires
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0075—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028—Shapes in the form of latin or greek characters
    • A61F2230/0054—V-shaped
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063—Three-dimensional shapes
    • A61F2230/0067—Three-dimensional shapes conical

Definitions

  • the present invention relates to medical implant insertion delivery systems and, more particularly, to a delivery device for vascular prostheses.
  • Medical implants in particular stent-based implants, can be deployed in the vasculature of patients to treat a variety of ailments and medical conditions.
  • the fragility of the vascular system tissue and the particular locations where a vascular prosthesis is required necessitates care and precision in the deployment of such implants.
  • heart related implants often comprising a valve body supported by a stent frame, present challenges in locating, positioning, and more specifically repositioning of the stent after partial or full deployment of the stent-based implant at a desired location.
  • a delivery device utilizes an outer sheath that is retracted to allow the implant to expand freely to a pre-determined diameter. However, again, once the frame is fully expanded, it cannot be collapsed to adjust, reposition, or remove the implant.
  • An additional short-coming with the noted delivery systems is that they are designed solely for use with their respective specific valve implant.
  • a further short-coming of such approaches is their reliance on radial force as the primary means of fixation and the inability to accurately position the implant during initial deployment.
  • the aforementioned devices consist of cylindrical frames, lacking features that can locate the implant relative to a native annulus of a heart valve. As a result, these devices must rely on external imaging during the delivery process, which can lead to improper placement of the implant and resulting complications and risks to the patient.
  • an improved medical implant delivery device that solves some of the disadvantages discussed above.
  • a delivery device that accurately positions an associated implant in a desired position such as, for example, a native valve annulus, controls the rate at which a frame expands, and allows the implant to be repositioned and adjusted after it has reached its full final diameter upon deployment, and before final release of the implant.
  • a need exists for an improved medical implant delivery device that does not require radial or longitudinal force applied and/or transferred to the abutting contact region of the vascular tissue within the patient.
  • the present invention provides a medical treatment system having an implant that can be positioned and deployed, then undeployed to allow repositioning of the implant while not requiring radial or longitudinal force to be applied to the desired contract region of the vascular system.
  • the present invention provides a medical treatment system comprising a first elongate support member having a distal mount, a second elongate support member having a proximal mount, the second elongate support member being selectively movable relative to the first elongate support member along a longitudinal axis, a self-expanding medical implant that foreshortens upon radially expanding from a radially compacted state, a distal interface configured to attach the distal mount to the implant, and a proximal interface configured to attach the proximal mount to the implant.
  • Moving the distal mount away from the proximal mount applies a longitudinal tension to the implant, causing the implant to expand longitudinally and contract radially and wherein moving the distal mount toward the proximal mount reduces a longitudinal tension in the implant allowing the implant to expand radially toward a fully expanded state.
  • the distal mount is attached to the distal interface by at least one distal flexible member and the proximal mount is attached to the proximal interface by at least one proximal flexible member.
  • the distal flexible member and the proximal flexible member comprise a suture.
  • the distal interface comprises at least one distal eyelet and the proximal interface comprises at least one proximal eyelet.
  • the medical treatment system additionally comprises a release mechanism configured to release the distal and proximal mounts from the implant.
  • the distal interface has a length and the implant has a length in the expanded state, and the distal interface length is at least the same as the implant length.
  • the medical treatment system additionally comprises an endoscope that extends through the first elongate support member so as to provide a view adjacent the distal end of the first elongate support member.
  • a controller controls the movement of the first elongate support member longitudinally relative the second elongate support member.
  • an actuator selectively moves the first elongate support member in a longitudinal direction relative to the second elongate support member.
  • the medical treatment system is in combination with a secondary restraint system.
  • the secondary restraint system comprises a sheath configured to hold the implant at least partially therein in a compacted state.
  • the present invention provides a medical treatment system that comprises a first elongate support member having a first engagement member and a second elongate support member having a second engagement member, the second elongate support member being selectively movable relative to the first elongate support member along a longitudinal axis.
  • the embodiment further includes a distal mount, a proximal mount slidingly coupled relative to the distal mount along the longitudinal axis, and a first spring interposed between the proximal and distal mounts so as to bias the proximal and distal mounts longitudinally away from one another.
  • the embodiment additionally includes a self-expanding medical implant that foreshortens upon radially expanding from a radially compacted state, a distal interface configured to attach the distal mount to the implant, and a proximal interface configured to attach the proximal mount to the implant.
  • a self-expanding medical implant that foreshortens upon radially expanding from a radially compacted state
  • a distal interface configured to attach the distal mount to the implant
  • a proximal interface configured to attach the proximal mount to the implant.
  • proximal and distal mounts are arranged between the first and second engagement members.
  • At least one of the proximal and distal interfaces comprises a ring assembly having at least one flexible arm fixedly attached to the ring at a first end and releasably attached to the implant at a second end, the second end extending beyond the diameter of the ring, and wherein the at least one flexible arm is resilient.
  • first and second engagement members are configured so that as the first and second engagement are moved toward one another, the proximal and distal mounts are urged toward each other and the biasing of the center spring is overcome so that the implant contracts longitudinally and expands radially.
  • a second spring is interposed between the second engagement member and one of the proximal and distal mounts
  • a third spring is interposed between the first engagement member and the other of the proximal and distal mounts, and the second and third springs each have a spring constant greater than a spring constant of the first spring.
  • the spring constants of the second and third springs are substantially the same.
  • the present invention provides a method of delivering a medical implant.
  • the method includes providing an implant delivery system comprising a self expanding implant configured to longitudinally foreshorten upon radially expanding from a compacted radial state, a delivery device comprising proximal and distal mounts that selectively connect to the implant by a proximal and a distal interface, respectively, the delivery device configured so that the proximal and distal mounts can be selectively moved relative to one another so as to selectively apply a longitudinal tension on the implant to urge the implant into the compacted radial state.
  • the embodiment further includes advancing the implant in a compacted radial state within a patient to a desired deployment location, positioning the implant adjacent the desired deployment location, actuating the delivery device so as to move the proximal and distal mounts toward one another so as to reduce the longitudinal tension on the implant and allow the implant to radially expand toward a fully expanded state, and verifying the implant is properly positioned at the desired deployment location within the patient.
  • Another embodiment wherein if it is determined that the implant is not properly positioned, additionally comprises moving the proximal and distal mounts away from one another so as to increase the longitudinal tension on the implant to longitudinally expand and radially contract the implant so as to disengage the implant from the patient's tissues.
  • a further such embodiment additionally comprises adjusting the position of the implant, and again moving the proximal and distal mounts toward one another so as to allow the implant to radially expand.
  • Yet another embodiment additionally comprises verifying whether the implant is poised to be properly positioned after partially expanding the implant.
  • a further embodiment additionally comprises providing an endoscope, and using the endoscope to verify whether the implant is properly positioned.
  • the principles discussed herein can be used in any application that would benefit from a prosthesis delivery device having repositioning capability and/or a reduced or negligible radial load transferred to the adjacent tissue surface during deployment of the prosthesis. While Applicant specifically provides examples of use of these principles in accordance with medical implant delivery devices and specifically delivery of stents, Applicant contemplates that other applications may benefit from this technology.
  • the medical treatment system 100 generally includes a controller 102, otherwise referred to as a handle, and a distal assembly 112.
  • the handle 102 includes a barrel 114 with a grip 110 located adjacent a proximal end of the barrel 114.
  • the handle 102 further includes an actuator 104 located adjacent a distal end of the barrel.
  • the barrel 114 is affixed to a top most portion of the grip 110.
  • An access to a lumen 106 is provided at the proximal end of the barrel 114.
  • the grip and barrel are sized to fit a typical physician's, or user's, hand to provide a stable grip and operating characteristics. Further, the shape and size of the barrel and grip are ergonomically shaped to provide a safe and reliable hold for the user.
  • the lumen 106 extends through the barrel 114 from the proximal end to the distal end, terminating at the actuator 104, and providing the outlet and coupling interface for a flexible portion 116, otherwise referred to as a proximal catheter.
  • the proximal catheter is coupled to the handle 102 at a proximal end and is coupled to the distal assembly 112 at a distal end, establishing mechanical communication between the handle and the distal assembly.
  • the actuator as depicted in the illustrated embodiment, includes a rotating knob 122 that, depending on the direction of rotation, will longitudinally move elements of the proximal catheter 116 relative the handle.
  • the elements of the proximal catheter 116 can be moved toward and into, or away and out of, the handle 102.
  • the proximal catheter can be substantially rigid, providing added control to the positioning of the distal assembly during the insertion and deployment operations discussed further below.
  • the distal assembly 112 is coupled to the handle 102 via the proximal catheter 116, the length of which can vary according to a physician's needs.
  • the proximal catheter includes a flexible extension tube 118, as shown in Figure 3A , and a flexible sheath 120.
  • the flexible sheath includes a through-hole, or lumen, disposed about a longitudinal axis along the full length of the sheath.
  • the flexible sheath provides a protective cover layer over the surface of the flexible extension tube 118, yet allows the flexible extension tube 118 to slidingly move longitudinally within the sheath.
  • the flexible extension tube is a catheter having a lumen disposed about a longitudinal axis.
  • the flexible extension tube proximal end is engagingly coupled to the actuator 104 and handle 102.
  • the flexible sheath proximal end is fixedly attached to the distal end of the barrel 114 adjacent the actuator 104.
  • the distal end of the flexible sheath is fixedly attached to the distal assembly 112.
  • the length of the flexible sheath establishes the distance between the handle 102 and the distal assembly.
  • the flexible extension tube and/or the flexible sheath can be substantially rigid.
  • the illustrated embodiment of medical treatment system 100 is generally intended for minimally invasive procedures, thus the free length of the proximal catheter 116 between the distal assembly 112 and the handle 102 is shorter than if the system were primarily directed to a percutaneous procedure to access a desired location for deployment of the medical implant.
  • the free length of the proximal catheter 116 can be longer, as the medical treatment system can be utilized in percutaneous procedures in alternative embodiments of the system.
  • the lumen 106 in addition to providing an extended path of motion for the proximal catheter 116 flexible extension tube 118, also provides a path and guideway for an endoscope 108.
  • the endoscope is used to provide a physician visual access adjacent to the distal assembly 112 during the deployment operation of the medical treatment system 100 and is directed through the lumen 106 and the flexible extension tube to the distal assembly.
  • FIG. 2A and 2B a front view of a medical implant 200, otherwise referred to as a stent, is shown.
  • the implant 200 is configured to allow foreshortening of the frame body upon the longitudinal contraction of the implant 200.
  • the implant 200 includes a frame 208, legs 210, otherwise referred to as anchors, a proximal interface 202, a distal interface 204, and an intermediate interface 206.
  • Figures 2A and 2B only show a frontside view of the implant 200 details, omitting the backside structure of the see-through device for clarity. Additionally, reference to implant 200 in further figures is depicted as a simpler cylinder shaped device for clarity and simplicity purposes only.
  • the illustrated implant 200 supports a heart valve body, and can be expanded from a compacted state as shown in Figure 2A to an expanded state as shown in Figure 2B .
  • the illustrated implant 200 preferably is a self-expanding stent constructed of a flexible material, preferably a shape memory material such as nitinol. As the implant is self-expanding, the implant 200 is in a fully opened state, as depicted in Figure 2B , when relaxed in an unrestrained condition.
  • the illustrated implant 200 preferably is elongate from a proximal end 212 to a distal end 214 and is tubular with a longitudinal axis 216 and a generally circular cross section.
  • stents can have a non-circular cross section, such as a D-shape, an oval or an otherwise ovoid cross-sectional shape.
  • a plurality of spaced apart proximal interfaces 202 are provided at the proximal end 212 and distal interfaces 204 are provided at the distal end 214 of the implant 200.
  • Other embodiments may be constructed without proximal or distal interfaces 202, 204.
  • the illustrated implant 200 has a non-foreshortening portion 218 and a foreshortening portion 220.
  • the portions are joined at a transition 222 between the proximal and distal ends 212, 214.
  • Foreshortening refers to a behavior in which the length of the implant 200 in the foreshortening portion 220 decreases as the radius of the stent increases from the compacted state to the expanded, deployed state.
  • Figure 2A which shows the implant 200 in a compacted state
  • the foreshortening portion 220 of the implant 200 is longer than when the stent is in the expanded state illustrated in Figure 2B .
  • the illustrated implant 200 has a plurality of anchors 210 that extend from the transition 222 into the foreshortening portion 220. Additional anchors 210 also extend from adjacent the distal end 214 into the foreshortening portion. The anchors extending in opposite directions establish a gap between their respective free ends, or proximal tip 234 and distal tip 236. The longitudinal contraction of the implant creates a corresponding movement of the anchor 210 that moves the proximal and distal tips closer together. The movement together allows the anchors 210 to grasp onto tissues at a desired location so as to hold the implant in place.
  • the non-foreshortening portion 218 of the illustrated implant 200 comprises a plurality of rows or rings 226a-c of circumferentially expansible elements, or struts 224, arranged in a zigzag pattern.
  • the struts 224 are configured to expand and contract with a change in radius of the implant 200.
  • the stent has three such rings 226a-c. It is to be understood that more or fewer rings can be employed as desired to accomplish the purposes of this stent frame.
  • each circumferential undulating strut 224 joins an adjacent strut 224 at an apex 228, 230 which is, in at least some embodiments, an area of preferential bending.
  • the zigzag pattern of a first 226a and a third ring 226c are generally in phase with one another, while the struts 224 of a second ring 226b between the first and third rings 226a, 226b are generally out of phase with those of the first and third rings. It is to be understood that, in other embodiments, all or most of the rings can be in phase with one another or out of phase as desired.
  • longitudinal struts 232 extend transversely across the rings 226a-c of the nonforeshortening portion 218 from the proximal end 212 of the implant 200 to the transition 222. More particularly, each ring 226 shares a common longitudinal strut 232.
  • the longitudinal struts 232 extend through apices 228 of adjacent rings 226, and preferably extend the entire length of the nonforeshortening portion 218.
  • the longitudinal struts 232 comprise a nonexpandable rod or bar.
  • the apices 228 that are connected to the longitudinal struts 232 are referred to as "connected" apices 228.
  • Apices 230 not connected to longitudinal struts 232 are referred to as "free" apices 230.
  • the longitudinal struts 232 are not substantially expandable in a longitudinal direction. As such, even though the undulating struts 224 provide flexibility in radial expansion or compaction, as the implant 200 changes radial size between the compacted and expanded states, the longitudinal length of the stent in the nonforeshortening portion 218 remains substantially unchanged.
  • the distal assembly includes the implant 200 and a delivery device 316.
  • the delivery device 316 further includes a proximal mount 300, a distal mount 302, a first elongate support member 304, a second elongate support member 306, a flanged sleeve 404, a distal collar 406, and a distal body 308.
  • the delivery device 316 is used to accurately and safely deliver and deploy the implant, or stent, adjacent a desired location within the patient.
  • the first elongate support member 304 is an elongate member preferably having a degree of flexibility but maintaining adequate stiffness to be axially loaded in compression and tension.
  • the pull rod 304 includes a lumen extending along its full length, similar to a common catheter.
  • the pull rod 304 is typically made of a flexibly capable bio-compatible material for use in the human body, e.g. silicone, polyurethane, polyethylene, polychloroethene, polytetrafluoroethylene, or the like.
  • the pull rod 304 is generally longer and extends distally beyond the distal end of the second elongate support member 306.
  • the distal end of the pull rod 304 includes an external thread 414 for coupling to an atraumatic nose cone or distal body 308, as discussed in detail below.
  • the proximal end of the pull rod is coupled to the proximal catheter 116 distal end via the flexible extension 118, also discussed in further detail below.
  • the second elongate support member 306 is a rigid cylinder having an inner diameter with a diametral magnitude at least the same as the pull rod 304, and a support 310 that is integral to the cylinder, as illustrated in Figure 4A .
  • the proximal stop 306 is typically made of a rigid bio-compatible material for use in the human body, e.g. titanium, stainless steel, thermoplastic or thermoset resins, ceramic, or the like.
  • the proximal stop 306 is shorter than the pull rod 306, generally being one to two times longer than the implant 200 although other varying lengths are possible.
  • the pull rod 304 is slidingly engaged within the inner diameter of the proximal stop 306, as described in detail below, and extends distally out of the distal end of the proximal stop 306 at least 1 ⁇ 2 to 2 times the longitudinal length of the implant when the distal assembly is in a longitudinally extended arrangement, or configuration.
  • the proximal mount 300 is a ring shaped device having an interior through-hole disposed about a longitudinal axis, an inner surface, an outer surface, a proximal face, a distal face, at least one guideslot 402, and an annular groove 602.
  • the through-hole establishes the diameter of the inner surface, and the inner surface diameter is substantially the same or slightly greater than the outer cylinder surface of a flanged sleeve 404, as depicted in the illustrated embodiment of Figure 4 .
  • the radial thickness of the proximal mount 300 preferably tapers from a thicker portion at the proximal face to a thinner portion at the distal face.
  • the proximal face of the proximal mount has a greater surface area, corresponding to the larger wall thickness of the ring member proximal end, as compared to the distal face of the proximal mount 300.
  • An annular groove 602, depicted in the illustrated embodiment of Figure 6 is located on the proximal face of the proximal mount 304.
  • the annular groove 602 extends all around the proximal face, encircling the through-hole about the longitudinal axis, and having a depth sufficient enough to receive a proximal ring 506.
  • the guideslot 402 is more clearly depicted in the illustrated embodiment of Figures 4 and 6 .
  • the at least one, or alternatively a plurality of, longitudinal grooves, or guideslots 402 are located on the outer surface of the proximal mount 304.
  • the guideslot preferably has a depth that is less than the total thickness of the proximal mount, and thus does not extend depthwise through to the inner surface of the proximal mount 300.
  • the plurality of guideslots 402 will generally be equally spaced circumferentially about the proximal mount, although any spacing arrangement is possible.
  • the proximal mount 300 and the distal mount 302 have similar or identical characteristics that are symmetric about the implant 200, thus in the illustrated embodiment the description of the proximal mount applies accordingly to the description characteristics of the distal mount except as expressly described.
  • the through-holes of the distal mount 302 and the proximal mount 304 can be different in diametral size where they are coupled to differing sized mounting elements, such as the diameter of the neck on the distal body 308, with which the distal mount is coupled, or the flanged sleeve 404, with which the proximal mount 300 is coupled, as described in detail below.
  • the flanged sleeve 404 is a substantially cylindrical member having a flange, or lip, portion protruding radially outward from the outer surface of the cylinder and located adjacent the distal end of the flanged sleeve 404.
  • the inner surface of the flanged sleeve 404 establishes a through-hole disposed about a longitudinal axis.
  • the diameter of the through-hole is substantially the same as, or slightly greater than, the outer surface diameter of the proximal stop 306.
  • the outer surface diameter of the proximal flanged sleeve cylindrical portion is substantially the same, or slightly less than, the inner surface diameter of the proximal mount 300.
  • the cylindrical body of the flanged sleeve 404 extends a longitudinal length that is longer than the longitudinal length of the proximal mount 300.
  • the distal collar 406 is a ring, similar to a washer or a nut, having a through-hole disposed about a longitudinal axis.
  • the longitudinal thickness of the collar 406 is sufficient to include internal fastener threads on the inner surface diameter of the through-hole.
  • the hole is sized substantially the same as pull rod 304.
  • the collar 406 is made from a rigid, bio-compatible material, e.g. metal, plastic, Teflon, or the like.
  • the collar can be fabricated from a flexible member that deflects radially outward further than a rigid collar yet sufficiently capable of retaining the distal mount on the nose cone, e.g. a radial spring, an elastic material such as rubber, or the like.
  • the distal body 308 otherwise referred to as a nose cone, as best shown in Figures 3 and 4 , is generally a cone or frustum shaped, bullet nosed structure with bulbous rounded surfaces to advantageously provide an atraumatic gentle entry and movement within the patient's vasculature and mitigate the risk of injury to adjacent tissue due to the insertion of the distal assembly 112 within the patient.
  • the cone shaped structure of the nose cone 308 is disposed about a longitudinal axis, with the larger diameter base of the cone located adjacent a proximal end of the nose cone 308 and the decreasing, tapering, or arcing, diameter extends to a generously rounded distal end, or tip, of the nose cone 308.
  • the nose cone 308 includes a through-hole disposed about the longitudinal axis along the full length from the proximal end to the distal end.
  • the through-hole diameter is similar in magnitude to the inner diameter of the pull rod 304.
  • the nose cone 308 proximal end, or proximal face 416 also includes a flange 408 and a neck 410 that extend proximally from the proximal end of the cone 308, and are substantially centrally disposed about the longitudinal axis of the nose cone 308.
  • the flange has a diameter smaller than the cone but larger than the neck.
  • the flange extends proximally a sufficient amount to create a shallow lip, such that a small gap exists when the distal mount is installed on the neck 410, as described in detail below.
  • the neck extends even further proximally, establishing a proximally protruding cylinder off of the nose cone 308.
  • the neck has a smaller outer diameter than the flange and also includes internal fastener threads adjacent the proximal end.
  • the through-hole of the nose cone 308 provides an access point for the endoscope 108, allowing the endoscope to pass through and exit out of the distal end, after which the endoscope 108 can then look back proximally on the distal assembly 112 and the implant 200 to provide visualization of the deployment process.
  • An alternative embodiment of the nose cone 308 includes an internal configuration providing an arcuate path, within the cone 308 itself, and exiting for example out of the side of the cone 308. Such a configuration routes the endoscope 108 viewing tip back toward the implant prior to exiting the distal end of the nose cone 308, placing the viewing tip nearer the implant.
  • the endoscope 108 can similarly exit any surface of the cone 308 that is sufficient to provide a visualization of the implant.
  • an aperture or viewing port can be formed in the pull rod 304 to enable an endoscope 108 to view the implant.
  • the side view of delivery device 316 further shows an embodiment of the support 310.
  • the support 310 is an integral lip extending all around the proximal stop 306 and located adjacent the proximal end of the proximal stop 306.
  • the support 310 has a substantially flat surface on the distal face, the face also being substantially normal to the longitudinal axis of the proximal stop 306.
  • the proximal face of the support 310 has a tapered surface extending from the radially outermost surface, or diameter, of the support 310 to the outer surface of the proximal stop 306 cylindrical surface.
  • the support 310 provides a physical stop and support for the proximal mount 300 disposed about the proximal stop 306, preventing the proximal mount from sliding or moving too far proximally as well as locating the proximal mount for installation of implant 200 onto delivery device 316.
  • the side view of delivery device 316 further shows the proximal flexible member 312, otherwise referred to as a proximal suture, and the distal flexible member 314, referred to as a distal suture.
  • the sutures 312, 314 attach the implant/stent 200 to the delivery device 316.
  • the length of the sutures 312, 314 can vary according to the size and location of the stent 200 and the delivery device 316.
  • the diameter of the sutures 312, 314 can vary as well, provided the sutures 312, 314 can sustain the tensile loads required for the implant installation and deployment process.
  • the sutures 312, 314 preferably are made of typical bio-compatible suture materials, e.g.
  • a plurality of sutures 312, 314 are used to attach the implant to the delivery device 316, as attachment is made at both the proximal and distal ends of the implant and the implant preferably is substantially centered about the delivery device 316.
  • the flexible members can have differing configuration, can be made of other materials, and may be substantially rigid.
  • a perspective view of selected details of the distal assembly 112 are shown, which includes a proximal ring 506, a distal ring 508, the proximal interface 202, and the distal interface 204, the anchor 210, and an annular groove 602.
  • the proximal ring 506 and the distal ring 508, otherwise referred to as proximal snap ring and distal snap ring, respectively, have similar characteristics in the illustrated embodiment; thus the description of features applies to both elements unless expressly described otherwise.
  • the proximal ring 506 is made of a small diameter member, generally a rigid bio-compatible material, e.g. metal, plastic, or the like, that is shaped to form a circle, where the circle generally lies on a common flat plane.
  • the small diameter member is formed in a circular manner such that the two ends of the member are adjacent each other, resulting in a slight gap between the ends.
  • the proximal ring 506 has a through-hole, establishing an inner diameter that is greater than the outer diameter of the cylindrical body of the flanged sleeve 404.
  • the diameter of the small diameter member is less than the wall thickness of the proximal end of the proximal mount 300.
  • the gap between the ends of the member provides access for the sutures 312 connection to the ring and subsequently to the delivery device 316.
  • there is no gap in the ring creating a continuous circle, whereby the sutures are individually tied onto the rings, or just folded over the ring and press fit into the annular groove, as discussed in further detail below, at the same time as the ring.
  • an embodiment of the implant 200 includes a plurality of the proximal interface 202 and the distal interface 204, as shown.
  • the proximal interface 202 establishes a connection, or attachment, location for the suture 312 and the distal interface 204 establishes an attachment location for the suture 314.
  • the proximal interface 202 and distal interface 204 in combination with the sutures 312, 314, connect the implant to the delivery device 316.
  • the shape and location of the interfaces 202, 204 can vary according to a physician's particular needs, and their shapes are not required to be identical, although such a configuration is possible. Their shape can be any three-dimensional geometry providing connection capability to the suture 312, e.g.
  • an eyelet as shown, a hook, a radiused or sharp angled triangle element, a block, a sphere, a t-shaped leg, or the like, and any combination thereof.
  • the suture contacting surfaces of the interfaces 202, 204 can vary as well, e.g. smooth, grooved, random discontinuous roughness, or the like, and any combination thereof.
  • the interfaces can be located anywhere on the implant instead of at the proximal and distal ends provided sufficient tension on the implant 200 can be achieved to obtain a reduced diametral cross-section of the implant, as discussed in detail below.
  • an intermediate interface 206 is provided just proximal the foreshortening portion.
  • proximal sutures connect to the intermediate interface, extend along the non-foreshortening portion and through the proximal interface, and then to the proximal mount 300.
  • the illustrated embodiment of the implant 200 has a plurality of anchors 210 for grasping the tissues of the vasculature at a desired location to hold the implant in place, as described in detail above.
  • anchors 210 for grasping the tissues of the vasculature at a desired location to hold the implant in place, as described in detail above.
  • other embodiments for other uses may not have anchors.
  • Distal assembly 112 is assembled to provide handle 102 controlled longitudinal displacement of the pull rod 304 and the nose cone 308.
  • the pull rod and the nose cone are rigidly coupled together and share a substantially common longitudinal axis extending through their respective through-holes, or lumens.
  • the coupling is achieved by way of the external thread 414 on the distal end of the pull rod 304, which threadingly engage the inner surface of the nose cone 308 through-hole, which includes a corresponding internal thread feature adjacent the nose cone proximal end.
  • the nose cone 308 prior to being coupled to the pull rod 304, is first coupled to the distal mount 302.
  • the distal mount 304 through-hole is received on the nose cone 308 neck that protrudes proximally.
  • the distal face of the distal mount 304 having the increased cylinder wall thickness, is abutted against the flat surface of the nose cone flange, which is orthogonal to the longitudinal axis of the neck, nose cone and distal mount 304, all of which are substantially co-axial.
  • the distal mount 304 is coupled via friction, where the diameters of the neck and the through-hole are sufficiently closely toleranced that a press fit occurs between the two details.
  • the distal mount 304 may be held in place by a distal collar 406, which is a ring or washer having sufficient thickness to be threaded on the inner surfaces of a through-hole extending along a longitudinal axis.
  • the through-hole is sized to threadingly engage the pull rod 304 external thread 414.
  • the distal mount 304 would be threadingly pressed between the distal collar 406 and the nose cone 308 flange as the external threads of the pull rod engage both the nose cone 308 and the distal collar.
  • the distal collar 406 can be frictionally press fit on the distal end of pull rod 304 to abut the proximal face of the distal mount 304.
  • the distal mount 304 is pressed between the nose cone 308 and the distal collar 406 by press fit friction and thread engagement, either alone or in combination.
  • the flanged sleeve 404 is configured to secure the proximal mount 300 onto the proximal stop 306.
  • the proximal mount 300 is first inserted onto the flanged sleeve 404, then the flanged sleeve 404 is inserted onto the proximal stop 306. Further details of the insertion steps are such that the through-hole of the proximal mount 300 is sized to fit snugly onto the cylindrical body of the flanged sleeve 404.
  • the proximal mount is initially inserted onto the proximal end of the sleeve 404 and slid distally until the distal face of the proximal mount abuts the radially outward protruding lip 412 of the sleeve 404.
  • the through-hole of the flanged sleeve 404 is sized to fit snugly, via friction of the two mating surfaces, onto the elongate cylinder surface of the proximal stop 306.
  • the proximal mount and the flanged sleeve can be an integral single-piece detail that achieves the described features and functions, eliminating the need for friction between the two details.
  • the sleeve 404 is then inserted onto the proximal stop 306 distal end and slidingly displaced proximally along the cylinder length toward the support 310.
  • a gap 'A' exists between the proximal face of the proximal mount, where gap 'A', as shown in Figure 3B , is established by the longer length accorded to the cylinder of the flanged sleeve 404 as compared to the longitudinal length of the proximal mount 300.
  • a proximal mount 300 moved all the way distally against the lip of the sleeve 404 will result in the proximal end of the flanged sleeve 404 creating the gap 'A' between support 310 and mount 300.
  • the pull rod 304 proximal end is coupled to the distal end of the flexible extension tube 118 of the proximal catheter 116, establishing longitudinal displacement capability and communication between the pull rod 306 and the handle 102.
  • the displacement capability is via the actuator 104, because the flexible extension tube 118 of the proximal catheter 116 proximal end is coupled to the actuator 104, the actuator 104 is located at the distal end of the handle 102, and actuating the actuator pushes the flexible extension tube 118 of the proximal catheter longitudinally.
  • the pull rod 304 proximal end terminates at the coupling to the flexible extension tube 118 of the proximal catheter 116 in the general area adjacent the proximal stop 306 proximal end when the delivery device 316 is assembled.
  • the pull rod 304 and the flexible extension tube 118 of the proximal catheter 116 extend through and slidingly engage within the proximal stop 306, however the pull rod 304 consumes the majority of the longitudinal length within the proximal stop 306 when the stop and the pull rod are in the un-extended longitudinal state, as shown in Figures 3A, 3B , and 4A .
  • Such a configuration advantageously establishes a level of stiffness between the proximal mount 300 and the distal mount 302 that are affixed to the proximal stop 306 and the pull rod 304, respectively, the portion of the delivery device that locates and deploys the implant 200.
  • the respective lengths, endpoints and connect locations between the proximal stop 306 and the pull rod 304 can vary such that the coupling does not occur adjacent the proximal stop proximal end, provided sufficient control of the implant 200 is achieved.
  • the proximal stop is not free to slide over the coupled flexible extension tube 118 and pull rod 306.
  • the flexible sheath 120 that covers and protects the flexible extension tube 118 and is fixedly attached to the handle 102 at the proximal end of the sheath 120, is abutted and/or coupled to the proximal end of the proximal stop 306 at the opposing distal end of the sheath 120.
  • proximal stop 306 the proximal mount 300, the flexible sheath 120, and the handle 102 are coupled together, effectively functioning as a single member in the assembled state, with the proximal stop 306 being a stiffer relative portion of the effective member as compared to the flexible sheath 120. All through-holes and inner diameters share substantially coincident longitudinal axes.
  • the nose cone 308, the distal mount 302, the pull rod 304, and the flexible extension tube 118 are coupled together, also effectively functioning as a single member.
  • the pull rod 304 is a stiffer relative portion of the effective member as compared to the flexible extension tube 118. All through-holes and inner diameters share substantially coincident longitudinal axes.
  • the effective single member comprising the pull rod 304 is the moving element, that moves relative the static proximal stop 306 effective member. The noted movement is controlled by the actuator 104, by proximally and distally moving the nose cone 308, the distal mount 302, and the pull rod 304 through interaction with the flexible extension tube 118.
  • the pull rod 304 and its effective member is in longitudinally movable communication with the handle 102, and is located within, and thus moves within, the through-hole inner diameter of the proximal stop 306 and its effective member.
  • the actuator 104 moves the pull rod 304 longitudinally relative the proximal stop 306 and its effective member of the handle 102, the flexible sheath 120, the proximal stop 306, and the proximal mount 300.
  • the pull rod 304 and the proximal stop 306 share the same longitudinal axis, their respective axes being substantially coincident. Thus, the two effective members move relative each other.
  • the pull rod 304 extends through the proximal stop 306 and the relative longitudinal motion is between the outer diameter surface of the pull rod 304 and the inner diameter surface of the proximal stop 306.
  • the increased stiffness of the proximal stop 306 and the pull rod 304 provides structural support to the distal assembly 112 that advantageously provides control during positioning and adjustment of the implant, as well as stability during any relative longitudinal motion between the proximal mount 300 and the distal mount 302.
  • the actuator 104 is coupled to the flexible extension tube 118, and actuation means occurs when the rotating knob 122 is rotated about the axis of the barrel 114, and the lumen 106.
  • the actuation means can be any mechanical or electromechanical method known in the art, e.g. thread engagement, spring and detent, worm drive, or the like. It is understood also that, in other embodiments, the actuator 104 can be configured differently in the controller 102, such as being a trigger or the like.
  • distal assembly 112 that readily positions, and is capable of readily repositioning, a medical implant at a desired location within a patient.
  • the distal assembly 112 advantageously provides for insertion, deployment and repositioning of the implant 200 without requiring external radial or longitudinal deployment forces that carry the risk of harming the tissue of and adjacent to the desired deployment location.
  • the stent 200 is temporarily secured by coupling means to the delivery device 316 for the insertion and deployment process, after which, when the implant is located as desired, the stent 200 is then removed from the delivery device 316.
  • the removal, or release of the coupling means, and the diameter of the delivery device allows the delivery device to be backed out of the insertion location safely, without harming the vascular tissue through which it passed to gain access to the desired location.
  • the delivery device 316 has the implant installed, as illustrated in Figures 3 , 5 , and 6 to establish a distal assembly 112 that is fully prepared for delivery and deployment within the patient's vasculature.
  • the installation of implant 200 utilizes the proximal interface 202, the proximal sutures 312, and the proximal ring 506 on the proximal side of the implant.
  • installation utilizes the distal interface 204, the distal sutures 314, and the distal ring 508.
  • the installation sequence for the proximal and distal ends of the implant 200 are identical, thus the description of the proximal end installation accordingly applies to the distal end of the implant 200.
  • the installation of the proximal end of implant 200 entails coupling the plurality of proximal sutures 312 to the proximal interface 202 and the proximal mount 300.
  • the connection to the proximal mount 300 occurs via a loop or a knot tied to the proximal ring 506, after which the proximal ring 506 is placed in the annular groove 602 and the suture is aligned in the guideslot 402 to complete the attachment.
  • the proximal suture 312 may be individually tied by a knot at each of the proximal interface 202 and the proximal mount, or can be looped through both with a a single knot tying both ends of the suture together. Variation can exist in where the individual knots are tied after individually looping the suture 312 through the proximal interface 202 and the proximal mount.
  • a knot can be placed adjacent the proximal mount 300 and the suture 312 simply looped through the proximal interface 202. This allows for a single cut of the suture to be made that releases the implant without leaving suture material attached to the implant, but ensures the suture 312 remains attached to the proximal mount upon removal of the delivery device 316 from the patient's vasculature.
  • proximal sutures are used to couple the proximal end of the implant 200 to the proximal mount 300, sufficiently spaced apart circumferentially about the longitudinal axis of the delivery device 316 such that the implant 200 is substantially centered about the axis.
  • Figure 3 illustrates the implant installed on the delivery device 316 in a longitudinally unrestrained condition, such that the diameter of the implant is at its self-expanding maximum.
  • the actuator 104 is actuated to extend, or displace outwardly from handle 102, the flexible extension tube 118.
  • the outward distal displacement is transmitted from the flexible extension tube 118 to the pull rod 304 and the distal mount 302.
  • This distal displacement of the distal mount 302 lengthens the delivery device 316 distance between the proximal mount 300 and the distal mount 302 which results in a longitudinal tension on the proximal and distal flexible members 312, 314 and thus, the implant 200.
  • the longitudinal tension applied to implant extends the longitudinal length and contracts the diameter of the implant 200 to a compacted state, as shown in Figure 7A .
  • the guideslots 402 are smaller than the diameter of the nose cone. This allows the sutures 312, 314 to be stretched in tension parallel to the longitudinal axis, which would result in a diameter of implant that approximates that of the sutures 312, 314.
  • the distal assembly 112 is then inserted, preferably in a minimally invasive manner, into the patient and the endoscope 108 is optionally inserted through the lumen 106, the flexible extension tube 118, the pull rod 304, and the nose cone 308 to provide visualization assistance during the positioning and deployment procedure.
  • the distal assembly is inserted into the vasculature and directed toward the desired location 702, which is the native annulus of the heart valve as illustrated in Figures 7A-B .
  • the implant 200 legs 210 are then centered about the desired location 702, as illustrated in Figure 7B , whereupon the actuator 104 is actuated to retract the flexible extension tube 118, which moves the distal mount 302 proximally toward the handle 102.
  • This longitudinal shortening of the delivery device 316 between the proximal mount 300 and the distal mount 302 allows the longitudinal length of the implant 200 to contract and the diameter of the implant to expand under the self-expanding properties of the implant.
  • the foreshortening portion of the implant is contracted and the legs 210 are drawn closer together so as to grasp the heart valve native annulus 702, as illustrated in Figure 7C .
  • the clinician verifies whether the implant has been properly positioned. In one embodiment, position is verified by using the endoscope as discussed above. Should repositioning be desired, the clinician actuates the actuator 104 to extend the distal mount 302 and pull rod 304 such that the implant again extends longitudinally and contracts diametrally, and as a result, disengages from its improperly positioned state.
  • the deployment process can be repeated after repositioning the implant 200 into an adjusted, desired location 702.
  • the delivery device 316 allows for the above described sequence of position, engage, and disengage, to be repeated until the implant 200 is properly positioned. It is to be understood that while making such adjustments, it may be sufficient to only partially radially contract the implant.
  • the delivery device 316 is removed from the implant and the patient's vasculature.
  • the removal sequence is initiated by severing the proximal sutures 312 as described above, leaving the totality of the sutures secured to the proximal mount 300 and ensuring no part of the sutures remain either free within the vasculature or attached to the implant 200 proximal interface 202.
  • the clinician can access, cut, and remove the proximal sutures while the delivery device remains in place.
  • Figure 8A illustrates the proximal sutures severed, with the proximal sutures not shown for clarity.
  • the delivery device may have a structure for detaching the sutures from the implant, yet retains the sutures so that they are removed from the patient with the device.
  • Severing of all the proximal sutures 312 allows partial retraction of the delivery device 316 by actuating the actuator 104 to retract the pull rod 304 in the proximal direction, bringing the distal mount 302 adjacent the proximal stop 300.
  • the entire system, except for the implant 200 can be moved proximally to further back the delivery device out of the interior of the implant 200.
  • the delivery device can not be fully removed yet, however, because the distal sutures remain attached to the implant 200.
  • the distal mounts are retracted proximally a sufficient distance relative the implant 200, as illustrated in Figure 8B , to allow sufficient clearance and access to the distal sutures 314 so they can be cut without necessitating entry of the cutting device into the interior of the implant 200.
  • such a sequence dictates a preferred sizing of the pull rod 304 whereby the longitudinal length of the pull rod 304 is sufficiently long enough that at full extension two preferred conditions are met.
  • First that there is sufficient internal overlap between the pull rod 306 and the proximate stop 304 such that adequate stiffness to maintain positioning control of the delivery device exists.
  • Second that the longitudinal length of the distal suture 314 is approximately at least as long as, and more preferably, 1 1 ⁇ 4 times as long as, the longitudinal length of the vasculature installed, or unrestrained, implant. The second condition ensures that the distal mount can move to a position so that severing of the distal sutures 314 can be performed without the cutting device entering the implant.
  • the sutures 312, 314 can be configured such that the sutures are disconnected from the implant by other structures and methods, such as the sutures disengaging by other mechanical action from the implant 200, knots being untied rather than severed, or the like. After the distal sutures 314 are severed, the delivery device 316 is free to move as a complete system proximally out of the vasculature and the patient, as illustrated in Figures 8C-D .
  • the disclosed embodiment uses spring mechanisms in conjunction with the handle 102 to control the deployment of the implant 200.
  • the spring mechanisms include a proximal spring 918, a distal spring 920, and an intermediate spring 916.
  • the proximal and distal springs 918, 920 are preferably helical compression springs, substantially similar in spring constant, diameter and longitudinal length.
  • Intermediate spring 916 is preferably a helical compression spring, similar in diameter to springs 918, 920 but has a spring constant that is less than that of proximal and distal springs 918, 920, thus requiring less compressive or tensile forces to compress or stretch the spring 920.
  • the illustrated embodiment further includes a first elongate support member 902 and a second elongate support member 904 that together control the longitudinal motion and displacement of the delivery device during the insertion and deployment of implant 200.
  • the first elongate support member 902 otherwise referred to as a mount tube
  • the illustrated embodiment of the second elongate support member 904 is a rigid tube in mechanical communication with a controller device such as handle 102 in a similar fashion as described above for distal assembly 112.
  • the pull rod 904 has an outer surface diameter such that the pull rod 904 fits inside of the mount tube 902 and can slidingly engage the mount tube inner diameter.
  • the distal mount 1002 typically integrally or fixedly attached to the distal end of the mount tube 1002, has a generally cylindrical shape that is coincident with the mount tube 902.
  • the distal mount 1002 includes at least one guideslot 1004, which is located on a proximal lip 1006, a groove 1008 that is disposed circumferentially about the distal mount 1002, and a distal lip 1010 located at the distal end of the mount tube 902.
  • the groove 1008 is further established by and located between the proximal lip 1006 and the distal lip 1010.
  • the guideslot 1004 extends longitudinally on the proximal lip 1006.
  • the illustrated embodiment further includes a proximal mount 906, a proximal body 912, a distal body 914, a proximal flexible member 908, and a distal flexible member 910.
  • the proximal mount 906, illustrated in detail in Figure 11 includes a proximal lip 1104, a groove 1102 that is disposed circumferentially about the proximal mount 906, a distal lip 1106, and at least one guideslot 1108.
  • the proximal mount 906 is configured in a similar arrangement as the distal mount 1002 except the proximal mount 906 includes a through-hole having a longitudinal axis that is sized to slidingly engage the outer surface diameter of the mount tube 902. Additionally, the proximal mount is symmetrically reversed longitudinally relative to the distal mount 1002, such that , for example, the guideslots are located on the distal end of the proximal mount 906.
  • the proximal flexible member 908, and the distal flexible member 910 are identical, comprised of a flexible member assembly 1200 as illustrated in Figure 12 , but symmetrically opposed on their common longitudinal axis about the implant 200 in the assembled arrangement.
  • the flexible member 1200 includes a plurality of arms 1202, and a ring 1204.
  • the arms 1202 are J-shaped wire-type elements, where the elongate portion is coupled to the ring 1204 and the radiused portion is biased to flare radially outward when the arms 1202 are in an unrestrained condition.
  • the ring 1204 has a longitudinal length and an inner and outer diameter that is configured to mate with the grooves 1102 and 1008 on the respective mounts.
  • the flexible member assembly 1200 preferably is comprised of a semi-rigid, or resiliently flexible material, e.g. metal, plastic, or the like. In alternative embodiments the flexible members can be substantially rigid and still provide the longitudinal tension required as described below.
  • the proximal body 912 includes two cylindrical portions, a smaller diameter cylinder sized to slidingly engage the mount tube 902 and the larger diameter cylinder sized to receive the proximal spring 918 and the proximal mount 906.
  • the distal body 914 as illustrated in Figure 13 includes a head 1300 having a conical shape similar to the nose cone 308 and a cylindrical body sized and configured to receive the distal spring 920 and the distal mount 1002.
  • the implant 200 preferably includes proximal and distal interfaces 202, 204 as described above.
  • the distal end of the pull rod 904 is coupled to the head 1300 of the distal body 914, within the through-hole lumen that is disposed about the longitudinal axis of the head 1300.
  • the distal spring 920 is disposed about the pull rod 904 and located between head 1300 and the distal mount 1002 within the cylindrical portion of the distal body 914.
  • the mount tube 902 has several details installed over the cylindrical tube.
  • Intermediate spring 916 is inserted on the proximal end of the mount tube 902 distally until contacting the proximal end of the distal mount 1002.
  • the distal end of the proximal mount 906 is placed onto the mount tube 902 and the mount 906 is slidingly engaged distally until contacting the proximal end of the intermediate spring 916.
  • the proximal spring 918 is then inserted in a like manner, followed by the larger diameter distal end of the proximal body 912.
  • the distal end of the proximal body 912 is inserted on the mount tube 902 until an inner orthogonal flat surface, which transitions the larger cylinder to the smaller cylinder of the body 912, contacts the proximal end of the proximal spring 918.
  • the flexible sheath 120 is then coupled to the proximal end of the proximal body 912, to establish a fixed distance between the proximal body and the controller 102.
  • the proximal and distal mounts 906, 1002 will also have the proximal and distal flexible members 908, 910 installed onto the respective mounts, such that the J-shaped arms are oriented to couple to the implant 200 at the proximal and distal interfaces 202, 204.
  • the distal spring 920 is then placed over the pull rod distal end, and finally the distal body 914 is coupled to the pull rod distal end.
  • the proximal mount 906 is effectively coupled to the distal mount 1002 via the distal flexible members 908, 910 and the implant 200, with the intermediate spring 916 located between the two mounts 906 and 1002.
  • the intermediate spring 916 urges the mounts longitudinally apart, which supplies tension to retain the implant 200 in a longitudinally extended and diametrally contracted configuration as shown.
  • the flexible sheath 120 abuts the proximal end of the proximal body 912.
  • longitudinal displacement of the pull rod 904 due to extraction or contraction via actuating of the actuator 104 occurs within the flexible sheath 120.
  • the mount tube 902 and the aforementioned installed details on the mount tube 902 essentially float between the nose cone 1300 and the flexible sheath 120. This floating condition allows for operation of the delivery device 900 to insert and deploy the implant 200.
  • the proximal body 912 is prevented from moving toward the handle 102 by the sheath 120.
  • the implant 200 installation on the delivery device 900 completes the assembly of the distal assembly 900, which is achieved as follows.
  • the intermediate spring 916 is compressed to hold the proximal and distal mounts close enough together to allow the arms 1202 to be coupled to the proximal and distal interfaces 202, 204 of the unrestrained self-expanded implant.
  • the implant 200 can be longitudinally extended in tension prior to the coupling to the flexible members to allow the interfaces to complete the coupling, or further still there can be a combination of the two, compression of intermediate spring 916 and longitudinal tensile extension of implant.
  • the intermediate spring is released and allowed to expand, extending the implant longitudinally, as the spring constant is chosen to be sufficient to overcome any resistance in the self-expanding implant to such longitudinal extension.
  • the delivery device is initially in the compacted state shown in Figure 15A .
  • the pull rod 904 distal end is coupled to the distal body 914 and the pull rod 904 proximal end is coupled to the actuator 104.
  • the actuator 104 is configured to move the pull rod 904 toward the handle 102 when actuated, so as to pull the distal body 914 toward the handle 102. bThis relative movement between the distal body 914 and proximal body 912 is resisted by each of the distal spring 920, proximal spring 918, and intermediate spring 916. However, because the intermediate spring 916 has a lower spring constant, the intermediate spring 916 will contract first before either the proximal or distal springs 918, 920.
  • the actuator 104 is actuated to begin the longitudinal contraction and engaging of the adjacent surfaces of the desired location 702 as described above, and as depicted in Figure 15B .
  • the distal assembly can be disengaged and repositioned as discussed above.
  • the delivery device 900 Upon successful deployment of the implant 200 the delivery device 900 is next removed from the implant by releasing the arms 1202 and extracting the delivery device. With particular reference next to Figure 15C , removal occurs by further actuation of the actuator 104 in a manner that moves the pull rod 904 distally away from the handle 102 and concurrently moves the distal body proximally toward the handle 102.
  • the intermediate spring 916 will eventually bottom out in compression and stop contracting.
  • the higher spring constant proximal and distal springs 918, 920 which did not contract previously because the spring constant is higher than the intermediate spring 916, will then contract under the continued compressive forces created by the distal motion of the actuator 104.
  • one or more physical stops are disposed on the mount tube 902 to stop further compression of the intermediate spring.
  • the distal body 914 and the proximal body 912 move toward the implant and the cylindrical bodies adjacent the implant 200 encompass the arms 1202 of the proximal and distal flexible members 908, 910.
  • the motion, combined with movement of the flexible member 908, 910 toward the center of the implant 200, of the cylindrical bodies encompassing the arms 1202 draws the arms radially inward toward the longitudinal axis, to be parallel to the inner diameter surface of the bodies. This motion brings the j-shaped radiused ends of the arms 1202 out of the proximal and distal interfaces 202, 204 of the implant.
  • the distal assembly is now free to be withdrawn from the interior of the implant and the patient's vasculature system.
  • the lumen extending through the delivery device 900 is not shown in the cross-section view of Figure 15E for clarity.
  • the delivery device includes a detent preventing movement of the pull rod 904 proximally to release the arms 1202. Once the clinician has verified the correct positioning of the implant 200, the detent may be actuated to allow further movement of the pull rod 904.
  • Figure 16A depicts one embodiment of a handle having an actuator 104 driven by rotation of an actuator knob 122.
  • Rotation of the knob 122 engages the flexible extension tube 118 of the proximal catheter 116 so as to longitudinally displace pull rod either proximally or distally, depending on the rotation direction of the knob.
  • the engagement can be applied by various methods, such as rotation of threads or the like.
  • a lever 1600 is optionally included and provides a secondary stop mechanism, such as a detent, that prevents actuation of the flexible extension tube 118 of the proximal catheter unless the lever 1600 is biased against the grip 110, which releases the detent stop mechanism and allows actuation of the proximal catheter.
  • a secondary stop mechanism such as a detent
  • a lever and spring loaded embodiment is shown to provide longitudinal displacement capability for the handle 102.
  • the handle 102 includes a lever 1600, and actuator spring 1602, and a locking mechanism 1604.
  • the lever 1600 extends downward from the distal side of the grip 110. This orientation allows a user to hold the grip 110 and concurrently actuate the lever proximally and distally about the connection pivot point that is located at the top of the grip 110 adjacent the barrel 114.
  • the spring 1602 is disposed within the barrel about the outer diameter surface of the lumen 106 and the proximal catheter 116.
  • the proximal end of the spring 1602 is coupled to the top end of the lever 1600 and the distal end of the spring 1602 is coupled to the distal end of the handle 102 or the barrel 114.
  • the spring is located in a compressed configuration, imparting a tensile force on the handle 102 and the lever 1602.
  • the tensile force of the spring 1602 biases the lever in a distal direction about its pivot connection to the handle 102.
  • the locking mechanism 1604 applies a friction force to the flexible extension tube 118 of the proximal catheter 116 preventing longitudinal displacement.
  • the lever 1600 moves the catheter and the spring 1602 biases the lever 1600 to the closed position, which is away from the grip 110, as shown in Figure 16B .
  • Actuation occurs when the lever 1600 is pulled toward the grip 110 and the lever pushes the proximal catheter distally, so as to also push the pull rod distally. Lock 1604 then holds the proximal catheter in place.
  • the sequence can be reversed, such as for the spring driven delivery device 900, such that actuation of the lever 1600 pulls on the flexible extension tube 118 of the proximal catheter to deploy the implant.
  • the lock 1604 can be configured to actuate a detent that prevents advancement or retraction beyond a specified distance, and the detent can be disengaged upon manipulation of the lock 1604.
  • the handle 1700 includes a knob 1702, a grip 1704, a dual spring 1708, and an actuator 1706.
  • the knob 1702 is coupled to a longitudinal neck that is further coupled to the flexible extension tube 118 of the proximal catheter 116.
  • the knob 1702 rests in the palm of the user, or physician.
  • the grip 1704 includes at least one radially extending arm that is held by the users fingers.
  • the actuator 1706 extends radially and is actuated by the users thumb. The actuation of the actuator 1706 engages the spring 1708 to selectively lock or allow actuation of the flexible extension tube of the proximal catheter in conjunction with the longitudinal depression of the knob 1702 by the user.
  • a pump of the lever 1600 or the knob 1702 or rotation of actuator knob 122 allows radial expansion of an associated implant by displacing the flexible extension tube 118 distally or proximally as appropriate.
  • the proximal and distal mounts 300 and 302 must move toward each other to allow the implant to diametrally expand and subsequently disengage from the implant 200. This is achieved by a plurality of means, both actively and passively.
  • the rotation of knob 122 allows precise control in both longitudinal directions.
  • the dual spring will contract and displace the flexible extension tube 118 of the proximal catheter 116 in the proximal direction.
  • An alternative method to the release mechanism is to utilize a detent that will establish a final click lock during the extension of the flexible extension tube 118, and such click with deploy and fix into longitudinal place the flexible extension tube 118.
  • a passive mechanism is possible that the mounts are displaced past the point of full expansion and then drop away to disengage freely from the implant 200.
  • the illustrated embodiments have been shown in the context of deploying an implant having a particular design. It is to be understood, however, that a variety of implant designs can be employed.
  • the illustrated implant included anchoring legs that would grasp tissue upon foreshortening during radial expansion. Other implant embodiments without anchoring legs can also be used with embodiments employing features discussed herein.
  • the illustrated implant has a foreshortening portion and a non-foreshortening portion. It is to be understood that other stent designs having greater- or lesser-sized foreshortening portions can be used, or even stents that have no non-foreshortening portion. Additionally, stents having other configurations of struts, cells and the like can be suitably employed.
  • features discussed herein can be combined with other implant delivery apparatus and methods.
  • the implant in addition to securing the implant under tension as in embodiments discussed above, the implant is also compacted and fit within a sheath, which helps to keep the implant in a small diametral configuration.
  • the sheath is located on the outer surface diameter of the implant and retains the implant in a diametrally constrained state. In such a configuration, the system holding the implant under tension is a primary restraint system and the sheath is part of a secondary restraint system.
  • the delivery device may include a secondary restraint structure comprising a line or ribbon extending from a portion of the delivery device and circumferentially encircling the outside of the implant between proximal and distal ends of the implant. At least one end of the line or ribbon can be tightened or let out by the operator manipulating the controller.
  • This secondary restraint works in concert with the proximal and distal mounts to control radial expansion of the implant, and when the proximal and distal mounts are moved toward one another, the clinician can simultaneously let out the ribbon so as to allow the implant to expand. Once the implant is deployed, the ribbon can be retracted into the delivery device and removed from the patient.

Landscapes

  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Transplantation (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Mechanical Engineering (AREA)
  • Prostheses (AREA)
  • Media Introduction/Drainage Providing Device (AREA)
EP14193715.1A 2008-10-01 2009-10-01 Système d'administration pour implant vasculaire Withdrawn EP2845569A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US13676008P 2008-10-01 2008-10-01
EP09737261.9A EP2341871B1 (fr) 2008-10-01 2009-10-01 Système de mise en place pour implant vasculaire

Related Parent Applications (2)

Application Number Title Priority Date Filing Date
EP09737261.9A Division EP2341871B1 (fr) 2008-10-01 2009-10-01 Système de mise en place pour implant vasculaire
EP09737261.9A Division-Into EP2341871B1 (fr) 2008-10-01 2009-10-01 Système de mise en place pour implant vasculaire

Publications (1)

Publication Number Publication Date
EP2845569A1 true EP2845569A1 (fr) 2015-03-11

Family

ID=41328427

Family Applications (2)

Application Number Title Priority Date Filing Date
EP14193715.1A Withdrawn EP2845569A1 (fr) 2008-10-01 2009-10-01 Système d'administration pour implant vasculaire
EP09737261.9A Active EP2341871B1 (fr) 2008-10-01 2009-10-01 Système de mise en place pour implant vasculaire

Family Applications After (1)

Application Number Title Priority Date Filing Date
EP09737261.9A Active EP2341871B1 (fr) 2008-10-01 2009-10-01 Système de mise en place pour implant vasculaire

Country Status (4)

Country Link
US (4) US8337541B2 (fr)
EP (2) EP2845569A1 (fr)
CA (1) CA2739275C (fr)
WO (1) WO2010040009A1 (fr)

Families Citing this family (210)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN1447669A (zh) 2000-08-18 2003-10-08 阿特里泰克公司 用于过滤从心房附件流出的血液的可膨胀植入装置
US20030050648A1 (en) 2001-09-11 2003-03-13 Spiration, Inc. Removable lung reduction devices, systems, and methods
US6592594B2 (en) 2001-10-25 2003-07-15 Spiration, Inc. Bronchial obstruction device deployment system and method
US20030216769A1 (en) 2002-05-17 2003-11-20 Dillard David H. Removable anchored lung volume reduction devices and methods
US20030181922A1 (en) 2002-03-20 2003-09-25 Spiration, Inc. Removable anchored lung volume reduction devices and methods
US7100616B2 (en) 2003-04-08 2006-09-05 Spiration, Inc. Bronchoscopic lung volume reduction method
US7533671B2 (en) 2003-08-08 2009-05-19 Spiration, Inc. Bronchoscopic repair of air leaks in a lung
US8951299B2 (en) 2003-12-23 2015-02-10 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US9526609B2 (en) 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US20120041550A1 (en) 2003-12-23 2012-02-16 Sadra Medical, Inc. Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements
US8343213B2 (en) 2003-12-23 2013-01-01 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US11278398B2 (en) 2003-12-23 2022-03-22 Boston Scientific Scimed, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US20050137687A1 (en) 2003-12-23 2005-06-23 Sadra Medical Heart valve anchor and method
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US8840663B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve method
US7959666B2 (en) 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US8828078B2 (en) 2003-12-23 2014-09-09 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8579962B2 (en) 2003-12-23 2013-11-12 Sadra Medical, Inc. Methods and apparatus for performing valvuloplasty
US7381219B2 (en) 2003-12-23 2008-06-03 Sadra Medical, Inc. Low profile heart valve and delivery system
DE102005003632A1 (de) 2005-01-20 2006-08-17 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Katheter für die transvaskuläre Implantation von Herzklappenprothesen
US7780723B2 (en) 2005-06-13 2010-08-24 Edwards Lifesciences Corporation Heart valve delivery system
AU2006315812B2 (en) 2005-11-10 2013-03-28 Cardiaq Valve Technologies, Inc. Balloon-expandable, self-expanding, vascular prosthesis connecting stent
US20070213813A1 (en) 2005-12-22 2007-09-13 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
CN101415379B (zh) 2006-02-14 2012-06-20 萨德拉医学公司 用于输送医疗植入物的***
US7691151B2 (en) 2006-03-31 2010-04-06 Spiration, Inc. Articulable Anchor
US20090306768A1 (en) 2006-07-28 2009-12-10 Cardiaq Valve Technologies, Inc. Percutaneous valve prosthesis and system and method for implanting same
US9408607B2 (en) * 2009-07-02 2016-08-09 Edwards Lifesciences Cardiaq Llc Surgical implant devices and methods for their manufacture and use
US7896915B2 (en) 2007-04-13 2011-03-01 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US9149379B2 (en) 2007-07-16 2015-10-06 Cook Medical Technologies Llc Delivery device
EP2194933B1 (fr) 2007-10-12 2016-05-04 Spiration, Inc. Procédé, système et appareil de chargement de valve
US9044318B2 (en) 2008-02-26 2015-06-02 Jenavalve Technology Gmbh Stent for the positioning and anchoring of a valvular prosthesis
BR112012021347A2 (pt) 2008-02-26 2019-09-24 Jenavalve Tecnology Inc stent para posicionamento e ancoragem de uma prótese valvular em um local de implantação no coração de um paciente
US9061119B2 (en) 2008-05-09 2015-06-23 Edwards Lifesciences Corporation Low profile delivery system for transcatheter heart valve
US8652202B2 (en) 2008-08-22 2014-02-18 Edwards Lifesciences Corporation Prosthetic heart valve and delivery apparatus
EP2367505B1 (fr) 2008-09-29 2020-08-12 Edwards Lifesciences CardiAQ LLC Valvule cardiaque
WO2010040009A1 (fr) 2008-10-01 2010-04-08 Cardiaq Valve Technologies, Inc. Système de mise en place pour implant vasculaire
JP5602151B2 (ja) 2008-12-30 2014-10-08 クック メディカル テクノロジーズ エルエルシー 給送器具
US8414644B2 (en) 2009-04-15 2013-04-09 Cardiaq Valve Technologies, Inc. Vascular implant and delivery system
US9730790B2 (en) 2009-09-29 2017-08-15 Edwards Lifesciences Cardiaq Llc Replacement valve and method
US8870950B2 (en) 2009-12-08 2014-10-28 Mitral Tech Ltd. Rotation-based anchoring of an implant
AU2011210747B2 (en) * 2010-01-29 2013-06-13 Cook Medical Technologies Llc Mechanically expandable delivery and dilation systems
WO2011111047A2 (fr) 2010-03-10 2011-09-15 Mitraltech Ltd. Valvule mitrale prothétique avec ancrages de tissus
US8623075B2 (en) 2010-04-21 2014-01-07 Medtronic, Inc. Transcatheter prosthetic heart valve delivery system and method with controlled expansion of prosthetic heart valve
US8579964B2 (en) 2010-05-05 2013-11-12 Neovasc Inc. Transcatheter mitral valve prosthesis
CA2799459A1 (fr) 2010-05-25 2011-12-01 Jenavalve Technology Inc. Valvule prothetique et endoprothese mise en place par catheterisme comprenant une valvule prothetique et un stent
CA2803149C (fr) 2010-06-21 2018-08-14 Impala, Inc. Prothese de valvule cardiaque
AU2011275468B2 (en) 2010-07-09 2014-02-06 Highlife Sas Transcatheter atrio-ventricular valve prosthesis
US9763657B2 (en) 2010-07-21 2017-09-19 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
US11653910B2 (en) 2010-07-21 2023-05-23 Cardiovalve Ltd. Helical anchor implantation
EP2444030A1 (fr) * 2010-08-31 2012-04-25 Biotronik AG Implant de valvule pour implantation dans un corps animal et/ou le corps humain
EP3342377B1 (fr) 2010-09-10 2022-06-15 Boston Scientific Limited Dispositifs de remplacement de valve, dispositif d'acheminement pour dispositif de remplacement de valve et procédé de fabrication d'un dispositif de remplacement de valve
US10321998B2 (en) 2010-09-23 2019-06-18 Transmural Systems Llc Methods and systems for delivering prostheses using rail techniques
WO2012040655A2 (fr) 2010-09-23 2012-03-29 Cardiaq Valve Technologies, Inc. Valvules prothétiques, dispositifs de pose et procédés afférents
US9579193B2 (en) 2010-09-23 2017-02-28 Transmural Systems Llc Methods and systems for delivering prostheses using rail techniques
DE102010050569A1 (de) * 2010-11-05 2012-05-10 Acandis Gmbh & Co. Kg Vorrichtung zum Entlassen eines selbstexpandierbaren medizinischen Funktionselements
US9155619B2 (en) 2011-02-25 2015-10-13 Edwards Lifesciences Corporation Prosthetic heart valve delivery apparatus
WO2012127309A1 (fr) 2011-03-21 2012-09-27 Ontorfano Matteo Appareil pour valvule à disques et procédé de traitement du dysfonctionnement de la valvule
US9554897B2 (en) 2011-04-28 2017-01-31 Neovasc Tiara Inc. Methods and apparatus for engaging a valve prosthesis with tissue
US9308087B2 (en) 2011-04-28 2016-04-12 Neovasc Tiara Inc. Sequentially deployed transcatheter mitral valve prosthesis
EP2520251A1 (fr) 2011-05-05 2012-11-07 Symetis SA Procédé et appareil pour compresser des valvules d'endoprothèse
US8795241B2 (en) 2011-05-13 2014-08-05 Spiration, Inc. Deployment catheter
GB2511375B (en) * 2011-05-13 2017-07-26 Spiration Inc Deployment Catheter
EP2726028B1 (fr) * 2011-06-30 2019-03-06 Cook Medical Technologies LLC Système de pose de stent commandé par un ressort
EP2731550B1 (fr) 2011-07-12 2016-02-24 Boston Scientific Scimed, Inc. Système de couplage pour une valvule de remplacement
US9339384B2 (en) 2011-07-27 2016-05-17 Edwards Lifesciences Corporation Delivery systems for prosthetic heart valve
US20140324164A1 (en) 2011-08-05 2014-10-30 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
WO2013021374A2 (fr) 2011-08-05 2013-02-14 Mitraltech Ltd. Techniques pour le remplacement et la fixation percutanés d'une valvule mitrale
US8852272B2 (en) 2011-08-05 2014-10-07 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
EP3417813B1 (fr) 2011-08-05 2020-05-13 Cardiovalve Ltd Remplacement percutané d'une valvule mitrale
US9549817B2 (en) 2011-09-22 2017-01-24 Transmural Systems Llc Devices, systems and methods for repairing lumenal systems
CN102488576B (zh) * 2011-11-25 2014-07-16 北京华脉泰科医疗器械有限公司 一种覆膜支架的输送释放装置
WO2013106585A1 (fr) * 2012-01-10 2013-07-18 White Jennifer K Structure de support articulée dotée d'éléments de renforcement secondaires
WO2013112547A1 (fr) 2012-01-25 2013-08-01 Boston Scientific Scimed, Inc. Ensemble de valvule avec un joint bioabsorbant et un implant de valvule remplaçable
US9078659B2 (en) * 2012-04-23 2015-07-14 Covidien Lp Delivery system with hooks for resheathability
US9345573B2 (en) 2012-05-30 2016-05-24 Neovasc Tiara Inc. Methods and apparatus for loading a prosthesis onto a delivery system
US9883941B2 (en) 2012-06-19 2018-02-06 Boston Scientific Scimed, Inc. Replacement heart valve
US8628571B1 (en) 2012-11-13 2014-01-14 Mitraltech Ltd. Percutaneously-deliverable mechanical valve
US9144492B2 (en) 2012-12-19 2015-09-29 W. L. Gore & Associates, Inc. Truncated leaflet for prosthetic heart valves, preformed valve
US9968443B2 (en) 2012-12-19 2018-05-15 W. L. Gore & Associates, Inc. Vertical coaptation zone in a planar portion of prosthetic heart valve leaflet
CA2896333C (fr) 2012-12-27 2021-01-12 Transcatheter Technologies Gmbh Appareil et ensemble de pliage et depliage d'un implant medical, comprenant un mecanisme de serrage
US20150351906A1 (en) 2013-01-24 2015-12-10 Mitraltech Ltd. Ventricularly-anchored prosthetic valves
US10583002B2 (en) 2013-03-11 2020-03-10 Neovasc Tiara Inc. Prosthetic valve with anti-pivoting mechanism
US9308108B2 (en) 2013-03-13 2016-04-12 Cook Medical Technologies Llc Controlled release and recapture stent-deployment device
US20140277427A1 (en) 2013-03-14 2014-09-18 Cardiaq Valve Technologies, Inc. Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
CN106691630A (zh) 2013-03-14 2017-05-24 斯波瑞申有限公司 瓣膜装载方法、***和装置
US9681951B2 (en) 2013-03-14 2017-06-20 Edwards Lifesciences Cardiaq Llc Prosthesis with outer skirt and anchors
US9730791B2 (en) 2013-03-14 2017-08-15 Edwards Lifesciences Cardiaq Llc Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
US9572665B2 (en) 2013-04-04 2017-02-21 Neovasc Tiara Inc. Methods and apparatus for delivering a prosthetic valve to a beating heart
US9763781B2 (en) * 2013-05-07 2017-09-19 George Kramer Inflatable transcatheter intracardiac devices and methods for treating incompetent atrioventricular valves
US8870948B1 (en) 2013-07-17 2014-10-28 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
EP3016595B1 (fr) 2013-07-26 2018-12-19 Edwards Lifesciences CardiAQ LLC Systèmes pour sceller des ouvertures dans une paroi anatomique
EP4098226A1 (fr) 2013-08-30 2022-12-07 JenaValve Technology, Inc. Endoprothèse comprenant une armature radialement repliable et une valve prothétique
US9925045B2 (en) 2013-10-21 2018-03-27 Medtronic Vascular Galway Systems, devices and methods for transcatheter valve delivery
CA2938614C (fr) 2014-02-21 2024-01-23 Edwards Lifesciences Cardiaq Llc Dispositif d'acheminement pour le deploiement maitrise d'une de valvule de substitution
USD755384S1 (en) 2014-03-05 2016-05-03 Edwards Lifesciences Cardiaq Llc Stent
US20170014115A1 (en) 2014-03-27 2017-01-19 Transmural Systems Llc Devices and methods for closure of transvascular or transcameral access ports
CA2948379C (fr) 2014-05-19 2022-08-09 J. Brent Ratz Valvule mitrale de remplacement ayant un rabat annulaire
US9532870B2 (en) 2014-06-06 2017-01-03 Edwards Lifesciences Corporation Prosthetic valve for replacing a mitral valve
WO2016016899A1 (fr) 2014-07-30 2016-02-04 Mitraltech Ltd. Prothèse valvulaire articulable
US10799359B2 (en) * 2014-09-10 2020-10-13 Cedars-Sinai Medical Center Method and apparatus for percutaneous delivery and deployment of a cardiac valve prosthesis
AU2015361260B2 (en) 2014-12-09 2020-04-23 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
WO2016126524A1 (fr) 2015-02-03 2016-08-11 Boston Scientific Scimed, Inc. Valve cardiaque prothétique à joint tubulaire
US9974651B2 (en) 2015-02-05 2018-05-22 Mitral Tech Ltd. Prosthetic valve with axially-sliding frames
CN107205818B (zh) 2015-02-05 2019-05-10 卡迪尔维尔福股份有限公司 带有轴向滑动框架的人工瓣膜
US10426617B2 (en) 2015-03-06 2019-10-01 Boston Scientific Scimed, Inc. Low profile valve locking mechanism and commissure assembly
US10441416B2 (en) 2015-04-21 2019-10-15 Edwards Lifesciences Corporation Percutaneous mitral valve replacement device
US10376363B2 (en) 2015-04-30 2019-08-13 Edwards Lifesciences Cardiaq Llc Replacement mitral valve, delivery system for replacement mitral valve and methods of use
EP3632378B1 (fr) 2015-05-01 2024-05-29 JenaValve Technology, Inc. Dispositif à faible débit de stimulateur cardiaque dans le remplacement de valvule cardiaque
EP4335415A3 (fr) 2015-05-14 2024-05-29 Cephea Valve Technologies, Inc. Valvules mitrales de remplacement
US10849746B2 (en) 2015-05-14 2020-12-01 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
WO2018136959A1 (fr) 2017-01-23 2018-07-26 Cephea Valve Technologies, Inc. Valves mitrales de remplacement
US10299950B2 (en) * 2015-05-20 2019-05-28 Cook Medical Technologies Llc Stent delivery system
CA2990872C (fr) 2015-06-22 2022-03-22 Edwards Lifescience Cardiaq Llc Implant de valve cardiaque pouvant etre commande de maniere active et procedes de commande de celui-ci
US10092400B2 (en) 2015-06-23 2018-10-09 Edwards Lifesciences Cardiaq Llc Systems and methods for anchoring and sealing a prosthetic heart valve
US10179046B2 (en) 2015-08-14 2019-01-15 Edwards Lifesciences Corporation Gripping and pushing device for medical instrument
WO2017035016A1 (fr) 2015-08-26 2017-03-02 Berkshire Grey Inc. Systèmes et procédés de fourniture de détection de contact dans un bras articulé
US10575951B2 (en) 2015-08-26 2020-03-03 Edwards Lifesciences Cardiaq Llc Delivery device and methods of use for transapical delivery of replacement mitral valve
US9889027B2 (en) 2015-08-26 2018-02-13 Cook Medical Technologies Llc Stent delivery system
US10117744B2 (en) 2015-08-26 2018-11-06 Edwards Lifesciences Cardiaq Llc Replacement heart valves and methods of delivery
US10350066B2 (en) 2015-08-28 2019-07-16 Edwards Lifesciences Cardiaq Llc Steerable delivery system for replacement mitral valve and methods of use
JP6869967B2 (ja) 2015-09-15 2021-05-12 ザ ユナイテッド ステイツ オブ アメリカ， アズ リプレゼンテッド バイ ザ セクレタリー， デパートメント オブ ヘルス アンド ヒューマン サービスＴｈｅ Ｕｎｉｔｅｄ Ｓｔａｔｅｓ Ｏｆ Ａｍｅｒｉｃａ， Ａｓ Ｒｅｐｒｅｓｅｎｔｅｄ Ｂｙ Ｔｈｅ Ｓｅｃｒｅｔａｒｙ， Ｄｅｐａｒｔｍｅｎｔ Ｏｆ Ｈｅａｌｔｈ Ａｎｄ Ｈｕｍａｎ Ｓｅｒｖｉｃｅ 経皮的グレン並びにフォンタン手術を実施するための装置及び方法
JP6854282B2 (ja) * 2015-09-18 2021-04-07 テルモ株式会社 押圧可能なインプラント送出システム
US10350067B2 (en) * 2015-10-26 2019-07-16 Edwards Lifesciences Corporation Implant delivery capsule
US11259920B2 (en) 2015-11-03 2022-03-01 Edwards Lifesciences Corporation Adapter for prosthesis delivery device and methods of use
US10321996B2 (en) 2015-11-11 2019-06-18 Edwards Lifesciences Corporation Prosthetic valve delivery apparatus having clutch mechanism
US10583007B2 (en) * 2015-12-02 2020-03-10 Edwards Lifesciences Corporation Suture deployment of prosthetic heart valve
CN113633435A (zh) 2016-01-29 2021-11-12 内奥瓦斯克迪亚拉公司 用于防止流出阻塞的假体瓣膜
US10531866B2 (en) 2016-02-16 2020-01-14 Cardiovalve Ltd. Techniques for providing a replacement valve and transseptal communication
US10799677B2 (en) 2016-03-21 2020-10-13 Edwards Lifesciences Corporation Multi-direction steerable handles for steering catheters
US11219746B2 (en) 2016-03-21 2022-01-11 Edwards Lifesciences Corporation Multi-direction steerable handles for steering catheters
US10799676B2 (en) 2016-03-21 2020-10-13 Edwards Lifesciences Corporation Multi-direction steerable handles for steering catheters
USD815744S1 (en) 2016-04-28 2018-04-17 Edwards Lifesciences Cardiaq Llc Valve frame for a delivery system
US20170325952A1 (en) * 2016-05-13 2017-11-16 Boston Scientific Scimed, Inc. Implant release system
CN109475419B (zh) 2016-05-13 2021-11-09 耶拿阀门科技股份有限公司 用于通过引导鞘和装载***来递送心脏瓣膜假体的心脏瓣膜假体递送***和方法
US10201416B2 (en) 2016-05-16 2019-02-12 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
WO2017218877A1 (fr) 2016-06-17 2017-12-21 Cephea Valve Technologies, Inc. Dispositifs et systèmes de mise en place de valve cardiaque
US10350062B2 (en) 2016-07-21 2019-07-16 Edwards Lifesciences Corporation Replacement heart valve prosthesis
US10646689B2 (en) 2016-07-29 2020-05-12 Cephea Valve Technologies, Inc. Mechanical interlock for catheters
US11324495B2 (en) 2016-07-29 2022-05-10 Cephea Valve Technologies, Inc. Systems and methods for delivering an intravascular device to the mitral annulus
US10639151B2 (en) 2016-07-29 2020-05-05 Cephea Valve Technologies, Inc. Threaded coil
US10974027B2 (en) 2016-07-29 2021-04-13 Cephea Valve Technologies, Inc. Combination steerable catheter and systems
US10661052B2 (en) 2016-07-29 2020-05-26 Cephea Valve Technologies, Inc. Intravascular device delivery sheath
USD800908S1 (en) 2016-08-10 2017-10-24 Mitraltech Ltd. Prosthetic valve element
CA3031187A1 (fr) 2016-08-10 2018-02-15 Cardiovalve Ltd. Valve prothetique avec cadres concentriques.
EP3500214A4 (fr) 2016-08-19 2019-07-24 Edwards Lifesciences Corporation Système de pose maniable pour valvule mitrale de remplacement et procédés d'utilisation
AU2017314852B2 (en) 2016-08-26 2022-06-30 Edwards Lifesciences Corporation Multi-portion replacement heart valve prosthesis
US10751485B2 (en) 2016-08-29 2020-08-25 Cephea Valve Technologies, Inc. Methods, systems, and devices for sealing and flushing a delivery system
US20180056043A1 (en) * 2016-08-29 2018-03-01 Randolf Von Oepen Adjustable guidewire receiving member
US11109967B2 (en) * 2016-08-29 2021-09-07 Cephea Valve Technologies, Inc. Systems and methods for loading and deploying an intravascular device
US10933216B2 (en) 2016-08-29 2021-03-02 Cephea Valve Technologies, Inc. Multilumen catheter
US11045315B2 (en) 2016-08-29 2021-06-29 Cephea Valve Technologies, Inc. Methods of steering and delivery of intravascular devices
US10874512B2 (en) 2016-10-05 2020-12-29 Cephea Valve Technologies, Inc. System and methods for delivering and deploying an artificial heart valve within the mitral annulus
US10849775B2 (en) * 2016-10-31 2020-12-01 Cook Medical Technologies Llc Suture esophageal stent introducer parallel handle
US10758348B2 (en) 2016-11-02 2020-09-01 Edwards Lifesciences Corporation Supra and sub-annular mitral valve delivery system
US10631981B2 (en) 2016-11-15 2020-04-28 Cephea Valve Technologies, Inc. Delivery catheter distal cap
CA3042588A1 (fr) 2016-11-21 2018-05-24 Neovasc Tiara Inc. Procedes et systemes de retraction rapide d'un systeme de pose de valvule cardiaque transcatheter
AU2018203053B2 (en) 2017-01-23 2020-03-05 Cephea Valve Technologies, Inc. Replacement mitral valves
CN110392557A (zh) 2017-01-27 2019-10-29 耶拿阀门科技股份有限公司 心脏瓣膜模拟
CN110381888B (zh) * 2017-03-09 2021-10-12 美敦力瓦斯科尔勒公司 用于带支架的假体递送装置的张力管理装置
BR112019021267A2 (pt) 2017-04-18 2020-05-19 Edwards Lifesciences Corp dispositivos de vedação de válvula cardíaca e dispositivos de liberação dos mesmos
US11224511B2 (en) 2017-04-18 2022-01-18 Edwards Lifesciences Corporation Heart valve sealing devices and delivery devices therefor
US10973634B2 (en) 2017-04-26 2021-04-13 Edwards Lifesciences Corporation Delivery apparatus for a prosthetic heart valve
US10959846B2 (en) 2017-05-10 2021-03-30 Edwards Lifesciences Corporation Mitral valve spacer device
WO2018226915A1 (fr) 2017-06-08 2018-12-13 Boston Scientific Scimed, Inc. Structure de support de commissure d'implant de valvule cardiaque
EP3644902B1 (fr) 2017-06-30 2024-05-22 Edwards Lifesciences Corporation Mécanismes de verrouillage et de déverrouillage pour dispositifs implantables trans-cathéters
EP3644903B1 (fr) 2017-06-30 2023-07-19 Edwards Lifesciences Corporation Valves transcathéter de stations d'accueil
WO2019010321A1 (fr) 2017-07-06 2019-01-10 Edwards Lifesciences Corporation Système de pose de rail maniable
US10857334B2 (en) 2017-07-12 2020-12-08 Edwards Lifesciences Corporation Reduced operation force inflator
US10898325B2 (en) 2017-08-01 2021-01-26 Boston Scientific Scimed, Inc. Medical implant locking mechanism
US10575948B2 (en) 2017-08-03 2020-03-03 Cardiovalve Ltd. Prosthetic heart valve
US11246704B2 (en) 2017-08-03 2022-02-15 Cardiovalve Ltd. Prosthetic heart valve
US10537426B2 (en) 2017-08-03 2020-01-21 Cardiovalve Ltd. Prosthetic heart valve
US11793633B2 (en) 2017-08-03 2023-10-24 Cardiovalve Ltd. Prosthetic heart valve
US10888421B2 (en) 2017-09-19 2021-01-12 Cardiovalve Ltd. Prosthetic heart valve with pouch
EP3668449A1 (fr) 2017-08-16 2020-06-24 Boston Scientific Scimed, Inc. Ensemble commissure de valvule cardiaque de remplacement
US10806573B2 (en) 2017-08-22 2020-10-20 Edwards Lifesciences Corporation Gear drive mechanism for heart valve delivery apparatus
WO2019036810A1 (fr) 2017-08-25 2019-02-28 Neovasc Tiara Inc. Prothèse de valvule mitrale transcathéter à déploiement séquentiel
US11051939B2 (en) 2017-08-31 2021-07-06 Edwards Lifesciences Corporation Active introducer sheath system
EP3687451B1 (fr) 2017-09-27 2023-12-13 Edwards Lifesciences Corporation Valvule prothétique à cadre extensible
US11109963B2 (en) 2017-09-27 2021-09-07 W. L. Gore & Associates, Inc. Prosthetic valves with mechanically coupled leaflets
JP7237955B2 (ja) 2017-10-18 2023-03-13 エドワーズ ライフサイエンシーズ コーポレイション カテーテルアセンブリ
US11207499B2 (en) 2017-10-20 2021-12-28 Edwards Lifesciences Corporation Steerable catheter
CA3078473C (fr) * 2017-10-31 2023-03-14 W. L. Gore & Associates, Inc. Systemes de deploiement par transcatheter et procedes associes
GB201720803D0 (en) 2017-12-13 2018-01-24 Mitraltech Ltd Prosthetic Valve and delivery tool therefor
GB201800399D0 (en) 2018-01-10 2018-02-21 Mitraltech Ltd Temperature-control during crimping of an implant
WO2019144069A2 (fr) 2018-01-19 2019-07-25 Boston Scientific Scimed, Inc. Capteurs de déploiement de mode d'inductance de système de valve transcathéter
WO2019144071A1 (fr) 2018-01-19 2019-07-25 Boston Scientific Scimed, Inc. Système de pose de dispositif médical à boucle de rétroaction
CN111818877B (zh) 2018-01-25 2023-12-22 爱德华兹生命科学公司 在部署后用于辅助置换瓣膜重新捕获和重新定位的递送***
WO2019157156A1 (fr) 2018-02-07 2019-08-15 Boston Scientific Scimed, Inc. Système de pose de dispositif médical avec élément d'alignement
WO2019165394A1 (fr) 2018-02-26 2019-08-29 Boston Scientific Scimed, Inc. Marqueur radio-opaque intégré dans un joint adaptatif
US11051934B2 (en) 2018-02-28 2021-07-06 Edwards Lifesciences Corporation Prosthetic mitral valve with improved anchors and seal
EP3793478A1 (fr) 2018-05-15 2021-03-24 Boston Scientific Scimed, Inc. Ensemble commissure de valvule cardiaque de remplacement
US11844914B2 (en) 2018-06-05 2023-12-19 Edwards Lifesciences Corporation Removable volume indicator for syringe
WO2019241477A1 (fr) 2018-06-13 2019-12-19 Boston Scientific Scimed, Inc. Dispositif de pose de valvule cardiaque de remplacement
JP7309855B2 (ja) * 2018-08-31 2023-07-18 ダブリュ．エル．ゴア アンド アソシエイツ，インコーポレイティド 埋植式医療装置のためのピボット送達システム
WO2020051591A1 (fr) * 2018-09-07 2020-03-12 Icahn School Of Medicine At Mount Sinai Système et procédé de pose de valve cardiaque à alignement rotatif
US11779728B2 (en) 2018-11-01 2023-10-10 Edwards Lifesciences Corporation Introducer sheath with expandable introducer
US11737872B2 (en) 2018-11-08 2023-08-29 Neovasc Tiara Inc. Ventricular deployment of a transcatheter mitral valve prosthesis
US11724068B2 (en) 2018-11-16 2023-08-15 Cephea Valve Technologies, Inc. Intravascular delivery system
US11241312B2 (en) 2018-12-10 2022-02-08 Boston Scientific Scimed, Inc. Medical device delivery system including a resistance member
CN113747863A (zh) 2019-03-08 2021-12-03 内奥瓦斯克迪亚拉公司 可取回假体递送***
WO2020206012A1 (fr) 2019-04-01 2020-10-08 Neovasc Tiara Inc. Valve prothétique déployable de manière contrôlable
US11491006B2 (en) 2019-04-10 2022-11-08 Neovasc Tiara Inc. Prosthetic valve with natural blood flow
US11439504B2 (en) 2019-05-10 2022-09-13 Boston Scientific Scimed, Inc. Replacement heart valve with improved cusp washout and reduced loading
WO2020236931A1 (fr) 2019-05-20 2020-11-26 Neovasc Tiara Inc. Dispositif d'introduction avec mécanisme d'hémostase
US11311376B2 (en) 2019-06-20 2022-04-26 Neovase Tiara Inc. Low profile prosthetic mitral valve
US12016774B2 (en) 2020-05-08 2024-06-25 Medtronic Vascular, Inc. Delivery system for prosthetic valve device having controlled release of inflow and outflow ends
BR112023002491A2 (pt) 2020-08-24 2023-05-02 Edwards Lifesciences Corp Métodos e sistemas para alinhar uma comissura de uma válvula cardíaca protética com uma comissura de uma válvula nativa
WO2022046319A1 (fr) 2020-08-31 2022-03-03 Edwards Lifesciences Corporation Systèmes et procédés d'aplatissement et de préparation de dispositif
US20240065864A1 (en) * 2022-08-30 2024-02-29 Boston Scientific Scimed, Inc. Endoprosthesis and methods for treating non-thrombotic iliac vein lesions

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2245495A (en) * 1990-05-11 1992-01-08 John Stanley Webber Artery support insertion instrument
US5411552A (en) 1990-05-18 1995-05-02 Andersen; Henning R. Valve prothesis for implantation in the body and a catheter for implanting such valve prothesis
US6168616B1 (en) * 1997-06-02 2001-01-02 Global Vascular Concepts Manually expandable stent
US6251093B1 (en) * 1991-07-16 2001-06-26 Heartport, Inc. Methods and apparatus for anchoring an occluding member
US6830584B1 (en) 1999-11-17 2004-12-14 Jacques Seguin Device for replacing a cardiac valve by percutaneous route
US20050283231A1 (en) * 2004-06-16 2005-12-22 Haug Ulrich R Everting heart valve
US20070250151A1 (en) * 2006-04-24 2007-10-25 Scimed Life Systems, Inc. Endovascular aortic repair delivery system with anchor

Family Cites Families (578)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US865203A (en) 1907-01-12 1907-09-03 Henry Mustonen Automatic coffee-roaster.
GB1264471A (fr) 1968-01-12 1972-02-23
US3671979A (en) 1969-09-23 1972-06-27 Univ Utah Catheter mounted artificial heart valve for implanting in close proximity to a defective natural heart valve
US3657744A (en) 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
GB1315844A (en) 1970-05-12 1973-05-02 Nat Res Dev Prosthetic cardiac valve
US3739402A (en) 1970-10-15 1973-06-19 Cutter Lab Bicuspid fascia lata valve
AR206762A1 (es) 1976-01-01 1976-08-13 Pisanu A Bioprotesis de bajo perfil derivada de la valvula aortica heterologa de porcino
US4056854A (en) 1976-09-28 1977-11-08 The United States Of America As Represented By The Department Of Health, Education And Welfare Aortic heart valve catheter
GB1603634A (en) 1977-05-05 1981-11-25 Nat Res Dev Prosthetic valves
US4265694A (en) 1978-12-14 1981-05-05 The United States Of America As Represented By The Department Of Health, Education And Welfare Method of making unitized three leaflet heart valve
US4222126A (en) 1978-12-14 1980-09-16 The United States Of America As Represented By The Secretary Of The Department Of Health, Education & Welfare Unitized three leaflet heart valve
US4340977A (en) 1980-09-19 1982-07-27 Brownlee Richard T Catenary mitral valve replacement
US4339831A (en) 1981-03-27 1982-07-20 Medtronic, Inc. Dynamic annulus heart valve and reconstruction ring
US4470157A (en) 1981-04-27 1984-09-11 Love Jack W Tricuspid prosthetic tissue heart valve
US4865600A (en) 1981-08-25 1989-09-12 Baxter International Inc. Mitral valve holder
BR8208063A (pt) 1981-09-16 1984-01-10 Hans Ivar Wallsten Dispositivo para aplicacao em vasos sanguineos ou outros locais de dificil acesso e seu emprego
EP0084395B1 (fr) 1982-01-20 1986-08-13 Martin Morris Black Valvules cardiaques artificielles
SE445884B (sv) 1982-04-30 1986-07-28 Medinvent Sa Anordning for implantation av en rorformig protes
US4477930A (en) 1982-09-28 1984-10-23 Mitral Medical International, Inc. Natural tissue heat valve and method of making same
US5067957A (en) 1983-10-14 1991-11-26 Raychem Corporation Method of inserting medical devices incorporating SIM alloy elements
US4733665C2 (en) 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4777951A (en) 1986-09-19 1988-10-18 Mansfield Scientific, Inc. Procedure and catheter instrument for treating patients for aortic stenosis
US4950227A (en) 1988-11-07 1990-08-21 Boston Scientific Corporation Stent delivery system
US4994077A (en) 1989-04-21 1991-02-19 Dobben Richard L Artificial heart valve for implantation in a blood vessel
US5439446A (en) * 1994-06-30 1995-08-08 Boston Scientific Corporation Stent and therapeutic delivery system
DK124690D0 (da) 1990-05-18 1990-05-18 Henning Rud Andersen Klapprotes til implantering i kroppen for erstatning af naturlig klap samt kateter til brug ved implantering af en saadan klapprotese
GB9012716D0 (en) 1990-06-07 1990-08-01 Frater Robert W M Mitral heart valve replacements
US5163955A (en) 1991-01-24 1992-11-17 Autogenics Rapid assembly, concentric mating stent, tissue heart valve with enhanced clamping and tissue alignment
US5197978B1 (en) 1991-04-26 1996-05-28 Advanced Coronary Tech Removable heat-recoverable tissue supporting device
USD484979S1 (en) 1991-06-28 2004-01-06 Cook Incorporated Implantable intravascular stent
USD390957S (en) 1992-03-09 1998-02-17 Cook Incorporated Implantable intravascular stent
US5370685A (en) 1991-07-16 1994-12-06 Stanford Surgical Technologies, Inc. Endovascular aortic valve replacement
US5332402A (en) 1992-05-12 1994-07-26 Teitelbaum George P Percutaneously-inserted cardiac valve
US6336938B1 (en) 1992-08-06 2002-01-08 William Cook Europe A/S Implantable self expanding prosthetic device
FR2694491B1 (fr) 1992-08-07 1994-09-30 Celsa Lg Filtres à pattes triangulées.
US5474563A (en) 1993-03-25 1995-12-12 Myler; Richard Cardiovascular stent and retrieval apparatus
US5843167A (en) 1993-04-22 1998-12-01 C. R. Bard, Inc. Method and apparatus for recapture of hooked endoprosthesis
ES2135520T3 (es) 1993-11-04 1999-11-01 Bard Inc C R Protesis vascular no migrante.
US5607444A (en) 1993-12-02 1997-03-04 Advanced Cardiovascular Systems, Inc. Ostial stent for bifurcations
US5522885A (en) 1994-05-05 1996-06-04 Autogenics Assembly tooling for an autologous tissue heart valve
EP1010406B1 (fr) 1994-06-08 2005-02-02 Cardiovascular Concepts, Inc. Greffe endoluminale
US5554185A (en) 1994-07-18 1996-09-10 Block; Peter C. Inflatable prosthetic cardiovascular valve for percutaneous transluminal implantation of same
US5397355A (en) 1994-07-19 1995-03-14 Stentco, Inc. Intraluminal stent
AU708360B2 (en) 1994-09-15 1999-08-05 C.R. Bard Inc. Hooked endoprosthesis
US5575818A (en) 1995-02-14 1996-11-19 Corvita Corporation Endovascular stent with locking ring
US5807398A (en) * 1995-04-28 1998-09-15 Shaknovich; Alexander Shuttle stent delivery catheter
US6602281B1 (en) 1995-06-05 2003-08-05 Avantec Vascular Corporation Radially expansible vessel scaffold having beams and expansion joints
WO1997014375A1 (fr) 1995-10-20 1997-04-24 Bandula Wijay Endoprothese vasculaire
US5843117A (en) 1996-02-14 1998-12-01 Inflow Dynamics Inc. Implantable vascular and endoluminal stents and process of fabricating the same
US6402780B2 (en) 1996-02-23 2002-06-11 Cardiovascular Technologies, L.L.C. Means and method of replacing a heart valve in a minimally invasive manner
EP1066804B1 (fr) 1996-03-05 2004-07-14 Evysio Medical Devices Ulc Stent extensible
DE69729137T2 (de) 1996-03-10 2005-05-12 Terumo K.K. Stent zur Implantation
US8036741B2 (en) 1996-04-30 2011-10-11 Medtronic, Inc. Method and system for nerve stimulation and cardiac sensing prior to and during a medical procedure
DE19619196A1 (de) 1996-05-11 1997-11-13 Pierburg Ag Elektromagnetisches Schaltventil
US5855601A (en) 1996-06-21 1999-01-05 The Trustees Of Columbia University In The City Of New York Artificial heart valve and method and device for implanting the same
DE19625202A1 (de) 1996-06-24 1998-01-02 Adiam Medizintechnik Gmbh & Co Prothetische Mitral-Herzklappe
DE19624948A1 (de) 1996-06-24 1998-01-02 Adiam Medizintechnik Gmbh & Co Prothetische Herzklappe
US5669919A (en) 1996-08-16 1997-09-23 Medtronic, Inc. Annuloplasty system
US5954764A (en) 1996-09-20 1999-09-21 Parodi; Juan Carlos Device for concurrently placing an endovascular expander with an endovascular prosthesis
US5725519A (en) 1996-09-30 1998-03-10 Medtronic Instent Israel Ltd. Stent loading device for a balloon catheter
NL1004827C2 (nl) 1996-12-18 1998-06-19 Surgical Innovations Vof Inrichting voor het reguleren van de bloedsomloop.
US7073504B2 (en) 1996-12-18 2006-07-11 Ams Research Corporation Contraceptive system and method of use
US6015431A (en) 1996-12-23 2000-01-18 Prograft Medical, Inc. Endolumenal stent-graft with leak-resistant seal
US5868782A (en) 1996-12-24 1999-02-09 Global Therapeutics, Inc. Radially expandable axially non-contracting surgical stent
EP0850607A1 (fr) 1996-12-31 1998-07-01 Cordis Corporation Prothèse de valve pour implantation dans des canaux corporels
US8353948B2 (en) 1997-01-24 2013-01-15 Celonova Stent, Inc. Fracture-resistant helical stent incorporating bistable cells and methods of use
US7241309B2 (en) 1999-04-15 2007-07-10 Scimed Life Systems, Inc. Self-aggregating protein compositions and use as sealants
US5928281A (en) 1997-03-27 1999-07-27 Baxter International Inc. Tissue heart valves
US5957949A (en) 1997-05-01 1999-09-28 World Medical Manufacturing Corp. Percutaneous placement valve stent
US6004328A (en) 1997-06-19 1999-12-21 Solar; Ronald J. Radially expandable intraluminal stent and delivery catheter therefore and method of using the same
US5810873A (en) 1997-07-15 1998-09-22 Advanced Cardiovascular Systems, Inc. Stent crimping tool and method of use
US8257725B2 (en) 1997-09-26 2012-09-04 Abbott Laboratories Delivery of highly lipophilic agents via medical devices
US6042606A (en) 1997-09-29 2000-03-28 Cook Incorporated Radially expandable non-axially contracting surgical stent
US5992000A (en) 1997-10-16 1999-11-30 Scimed Life Systems, Inc. Stent crimper
US5935108A (en) 1997-11-14 1999-08-10 Reflow, Inc. Recanalization apparatus and devices for use therein and method
US6352543B1 (en) 2000-04-29 2002-03-05 Ventrica, Inc. Methods for forming anastomoses using magnetic force
EP2108377A1 (fr) 1998-03-24 2009-10-14 Chugai Seiyaku Kabushiki Kaisha Inhibiteurs de vascularisation
US20040254635A1 (en) 1998-03-30 2004-12-16 Shanley John F. Expandable medical device for delivery of beneficial agent
US6520983B1 (en) 1998-03-31 2003-02-18 Scimed Life Systems, Inc. Stent delivery system
US7713297B2 (en) 1998-04-11 2010-05-11 Boston Scientific Scimed, Inc. Drug-releasing stent with ceramic-containing layer
US6132458A (en) 1998-05-15 2000-10-17 American Medical Systems, Inc. Method and device for loading a stent
US6613059B2 (en) 1999-03-01 2003-09-02 Coalescent Surgical, Inc. Tissue connector apparatus and methods
US6260552B1 (en) 1998-07-29 2001-07-17 Myocor, Inc. Transventricular implant tools and devices
WO2000015147A1 (fr) 1998-09-10 2000-03-23 Percardia, Inc. Shunt tmr
US6214054B1 (en) 1998-09-21 2001-04-10 Edwards Lifesciences Corporation Method for fixation of biological tissues having mitigated propensity for post-implantation calcification and thrombosis and bioprosthetic devices prepared thereby
US8257724B2 (en) 1998-09-24 2012-09-04 Abbott Laboratories Delivery of highly lipophilic agents via medical devices
US7044134B2 (en) 1999-11-08 2006-05-16 Ev3 Sunnyvale, Inc Method of implanting a device in the left atrial appendage
US6113612A (en) 1998-11-06 2000-09-05 St. Jude Medical Cardiovascular Group, Inc. Medical anastomosis apparatus
US6152937A (en) 1998-11-06 2000-11-28 St. Jude Medical Cardiovascular Group, Inc. Medical graft connector and methods of making and installing same
US6322585B1 (en) 1998-11-16 2001-11-27 Endotex Interventional Systems, Inc. Coiled-sheet stent-graft with slidable exo-skeleton
US6733523B2 (en) 1998-12-11 2004-05-11 Endologix, Inc. Implantable vascular graft
US6896690B1 (en) 2000-01-27 2005-05-24 Viacor, Inc. Cardiac valve procedure methods and devices
WO2000044313A1 (fr) 1999-01-27 2000-08-03 Viacor Incorporated Procedes et dispositifs pour interventions sur valvules cardiaques
US7018401B1 (en) 1999-02-01 2006-03-28 Board Of Regents, The University Of Texas System Woven intravascular devices and methods for making the same and apparatus for delivery of the same
US6425916B1 (en) 1999-02-10 2002-07-30 Michi E. Garrison Methods and devices for implanting cardiac valves
WO2000053104A1 (fr) 1999-03-09 2000-09-14 St. Jude Medical Cardiovascular Group, Inc. Procedes et appareil de greffe medicale
US6325825B1 (en) 1999-04-08 2001-12-04 Cordis Corporation Stent with variable wall thickness
US8216256B2 (en) 1999-04-09 2012-07-10 Evalve, Inc. Detachment mechanism for implantable fixation devices
US7147663B1 (en) 1999-04-23 2006-12-12 St. Jude Medical Atg, Inc. Artificial heart valve attachment apparatus and methods
US6245101B1 (en) 1999-05-03 2001-06-12 William J. Drasler Intravascular hinge stent
US6712836B1 (en) 1999-05-13 2004-03-30 St. Jude Medical Atg, Inc. Apparatus and methods for closing septal defects and occluding blood flow
US6858034B1 (en) 1999-05-20 2005-02-22 Scimed Life Systems, Inc. Stent delivery system for prevention of kinking, and method of loading and using same
US6790229B1 (en) 1999-05-25 2004-09-14 Eric Berreklouw Fixing device, in particular for fixing to vascular wall tissue
US6312465B1 (en) 1999-07-23 2001-11-06 Sulzer Carbomedics Inc. Heart valve prosthesis with a resiliently deformable retaining member
US6749606B2 (en) 1999-08-05 2004-06-15 Thomas Keast Devices for creating collateral channels
US20010047200A1 (en) 1999-10-13 2001-11-29 Raymond Sun Non-foreshortening intraluminal prosthesis
US6440164B1 (en) 1999-10-21 2002-08-27 Scimed Life Systems, Inc. Implantable prosthetic valve
US6551303B1 (en) 1999-10-27 2003-04-22 Atritech, Inc. Barrier device for ostium of left atrial appendage
GB9925636D0 (en) 1999-10-29 1999-12-29 Angiomed Ag Method of, and device for, installing a stent in a sleeve
US7018406B2 (en) 1999-11-17 2006-03-28 Corevalve Sa Prosthetic valve for transluminal delivery
US20070043435A1 (en) 1999-11-17 2007-02-22 Jacques Seguin Non-cylindrical prosthetic valve system for transluminal delivery
FR2815844B1 (fr) 2000-10-31 2003-01-17 Jacques Seguin Support tubulaire de mise en place, par voie percutanee, d'une valve cardiaque de remplacement
US8016877B2 (en) 1999-11-17 2011-09-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8579966B2 (en) 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US6458153B1 (en) 1999-12-31 2002-10-01 Abps Venture One, Ltd. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
US6280466B1 (en) 1999-12-03 2001-08-28 Teramed Inc. Endovascular graft system
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US7749245B2 (en) 2000-01-27 2010-07-06 Medtronic, Inc. Cardiac valve procedure methods and devices
US6872226B2 (en) 2001-01-29 2005-03-29 3F Therapeutics, Inc. Method of cutting material for use in implantable medical device
EP1255510B3 (fr) 2000-01-31 2009-03-04 Cook Biotech, Inc. Valvules sur stents
US6797002B2 (en) 2000-02-02 2004-09-28 Paul A. Spence Heart valve repair apparatus and methods
DE10010074B4 (de) 2000-02-28 2005-04-14 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Vorrichtung zur Befestigung und Verankerung von Herzklappenprothesen
IL153753A0 (en) 2002-12-30 2003-07-06 Neovasc Medical Ltd Varying-diameter vascular implant and balloon
US6953476B1 (en) 2000-03-27 2005-10-11 Neovasc Medical Ltd. Device and method for treating ischemic heart disease
US6454799B1 (en) 2000-04-06 2002-09-24 Edwards Lifesciences Corporation Minimally-invasive heart valves and methods of use
US6517573B1 (en) 2000-04-11 2003-02-11 Endovascular Technologies, Inc. Hook for attaching to a corporeal lumen and method of manufacturing
US20020049490A1 (en) 2000-04-11 2002-04-25 Pollock David T. Single-piece endoprosthesis with high expansion ratios
US6610088B1 (en) 2000-05-03 2003-08-26 Shlomo Gabbay Biologically covered heart valve prosthesis
MXPA02011590A (es) 2000-05-25 2004-07-30 Bioring S A Dispositivo para estrechar y/o reforzar los orificios valvulares del corazon.
US8366769B2 (en) 2000-06-01 2013-02-05 Edwards Lifesciences Corporation Low-profile, pivotable heart valve sewing ring
US6358277B1 (en) 2000-06-21 2002-03-19 The International Heart Institute Of Montana Foundation Atrio-ventricular valvular device
US6695878B2 (en) 2000-06-26 2004-02-24 Rex Medical, L.P. Vascular device for valve leaflet apposition
US6527800B1 (en) 2000-06-26 2003-03-04 Rex Medical, L.P. Vascular device and method for valve leaflet apposition
US6676698B2 (en) 2000-06-26 2004-01-13 Rex Medicol, L.P. Vascular device with valve for approximating vessel wall
WO2002019951A1 (fr) 2000-09-07 2002-03-14 Viacor, Inc. Bande de fixation pour fixer une valvule cardiaque prothetique au tissu
US7510572B2 (en) 2000-09-12 2009-03-31 Shlomo Gabbay Implantation system for delivery of a heart valve prosthesis
WO2002022054A1 (fr) 2000-09-12 2002-03-21 Gabbay S Prothese valvulaire et son procede d'utilisation
DE10046550A1 (de) 2000-09-19 2002-03-28 Adiam Life Science Ag Prothetische Mitral-Herzklappe
WO2004030570A2 (fr) 2002-10-01 2004-04-15 Ample Medical, Inc. Dispositifs, systemes et procedes pour maintenir un feuillet de valvule cardiaque natif
US6893459B1 (en) 2000-09-20 2005-05-17 Ample Medical, Inc. Heart valve annulus device and method of using same
US7163552B2 (en) * 2000-10-13 2007-01-16 Medtronic Vascular, Inc. Stent delivery system with hydraulic deployment
US6936058B2 (en) 2000-10-18 2005-08-30 Nmt Medical, Inc. Over-the-wire interlock attachment/detachment mechanism
US6482228B1 (en) 2000-11-14 2002-11-19 Troy R. Norred Percutaneous aortic valve replacement
US6974476B2 (en) 2003-05-05 2005-12-13 Rex Medical, L.P. Percutaneous aortic valve
US6929660B1 (en) 2000-12-22 2005-08-16 Advanced Cardiovascular Systems, Inc. Intravascular stent
US7208002B2 (en) 2001-01-04 2007-04-24 Boston Scientific Scimed, Inc. Expansion-assisting delivery system for self-expanding stent
US20050182483A1 (en) 2004-02-11 2005-08-18 Cook Incorporated Percutaneously placed prosthesis with thromboresistant valve portion
US6733525B2 (en) 2001-03-23 2004-05-11 Edwards Lifesciences Corporation Rolled minimally-invasive heart valves and methods of use
US7556646B2 (en) 2001-09-13 2009-07-07 Edwards Lifesciences Corporation Methods and apparatuses for deploying minimally-invasive heart valves
US6764505B1 (en) 2001-04-12 2004-07-20 Advanced Cardiovascular Systems, Inc. Variable surface area stent
DE10121210B4 (de) 2001-04-30 2005-11-17 Universitätsklinikum Freiburg Verankerungselement zur intraluminalen Verankerung eines Herzklappenersatzes und Verfahren zu seiner Herstellung
WO2002087474A1 (fr) 2001-05-01 2002-11-07 Imperial Medical Devices Limited Prothese de valvule
US7935145B2 (en) 2001-05-17 2011-05-03 Edwards Lifesciences Corporation Annuloplasty ring for ischemic mitral valve insuffuciency
ITMI20011012A1 (it) 2001-05-17 2002-11-17 Ottavio Alfieri Protesi anulare per valvola mitrale
US7087088B2 (en) 2001-05-24 2006-08-08 Torax Medical, Inc. Methods and apparatus for regulating the flow of matter through body tubing
US6926732B2 (en) 2001-06-01 2005-08-09 Ams Research Corporation Stent delivery device and method
WO2002100454A1 (fr) 2001-06-11 2002-12-19 Boston Scientific Limited Prothese composite eptfe/textile
US8771302B2 (en) 2001-06-29 2014-07-08 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US7544206B2 (en) 2001-06-29 2009-06-09 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US7547322B2 (en) 2001-07-19 2009-06-16 The Cleveland Clinic Foundation Prosthetic valve and method for making same
FR2828091B1 (fr) 2001-07-31 2003-11-21 Seguin Jacques Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel
FR2828263B1 (fr) 2001-08-03 2007-05-11 Philipp Bonhoeffer Dispositif d'implantation d'un implant et procede d'implantation du dispositif
DE10148185B4 (de) 2001-09-28 2005-08-11 Alveolus, Inc. Instrument zum Implantieren von Gefäßprothesen
AU2002337598A1 (en) 2001-10-04 2003-04-14 Neovasc Medical Ltd. Flow reducing implant
US6893460B2 (en) 2001-10-11 2005-05-17 Percutaneous Valve Technologies Inc. Implantable prosthetic valve
US7192766B2 (en) 2001-10-23 2007-03-20 Medtronic Minimed, Inc. Sensor containing molded solidified protein
GB0125925D0 (en) 2001-10-29 2001-12-19 Univ Glasgow Mitral valve prosthesis
US20030176914A1 (en) 2003-01-21 2003-09-18 Rabkin Dmitry J. Multi-segment modular stent and methods for manufacturing stents
US7294146B2 (en) 2001-12-03 2007-11-13 Xtent, Inc. Apparatus and methods for delivery of variable length stents
US20030105517A1 (en) 2001-12-05 2003-06-05 White Geoffrey Hamilton Non-foreshortening stent
US20080249504A1 (en) 2007-04-06 2008-10-09 Lattouf Omar M Instrument port
US7147661B2 (en) 2001-12-20 2006-12-12 Boston Scientific Santa Rosa Corp. Radially expandable stent
US6641606B2 (en) 2001-12-20 2003-11-04 Cleveland Clinic Foundation Delivery system and method for deploying an endovascular prosthesis
US6682537B2 (en) 2001-12-20 2004-01-27 The Cleveland Clinic Foundation Apparatus and method for capturing a wire in a blood vessel
US7014653B2 (en) 2001-12-20 2006-03-21 Cleveland Clinic Foundation Furcated endovascular prosthesis
EP2277474A3 (fr) 2001-12-20 2013-11-27 TriVascular, Inc. Greffe endovasculaire évoluée
US8123801B2 (en) 2001-12-21 2012-02-28 QuickRing Medical Technologies, Ltd. Implantation system for annuloplasty rings
US7201771B2 (en) 2001-12-27 2007-04-10 Arbor Surgical Technologies, Inc. Bioprosthetic heart valve
US7033390B2 (en) 2002-01-02 2006-04-25 Medtronic, Inc. Prosthetic heart valve system
US6878168B2 (en) 2002-01-03 2005-04-12 Edwards Lifesciences Corporation Treatment of bioprosthetic tissues to mitigate post implantation calcification
US20030130729A1 (en) 2002-01-04 2003-07-10 David Paniagua Percutaneously implantable replacement heart valve device and method of making same
US8308797B2 (en) 2002-01-04 2012-11-13 Colibri Heart Valve, LLC Percutaneously implantable replacement heart valve device and method of making same
EP1469794B1 (fr) 2002-01-28 2009-03-18 OrbusNeich Medical, Inc. Endoprothese ostiale evasee et systeme d'apport
US20030199971A1 (en) 2002-04-23 2003-10-23 Numed, Inc. Biological replacement valve assembly
US8721713B2 (en) 2002-04-23 2014-05-13 Medtronic, Inc. System for implanting a replacement valve
WO2003092554A1 (fr) 2002-05-03 2003-11-13 The General Hospital Corporation Valvule endovasculaire involutee et procede de construction associe
US20030220683A1 (en) 2002-05-22 2003-11-27 Zarouhi Minasian Endoluminal device having barb assembly and method of using same
US7044962B2 (en) 2002-06-25 2006-05-16 Scimed Life Systems, Inc. Implantable prosthesis with displaceable skirt
US7959674B2 (en) 2002-07-16 2011-06-14 Medtronic, Inc. Suture locking assembly and method of use
US20060106449A1 (en) 2002-08-08 2006-05-18 Neovasc Medical Ltd. Flow reducing implant
EP1534180A4 (fr) 2002-08-08 2007-04-04 Neovasc Medical Ltd Regulateur de debit de forme geometrique
RU2005108673A (ru) 2002-08-29 2006-01-20 Митралсолюшнз, Инк. (Us) Имплантируемые устройства для регулирования внутренней окружности анатомического отверстия или просвета
US6875231B2 (en) 2002-09-11 2005-04-05 3F Therapeutics, Inc. Percutaneously deliverable heart valve
CO5500017A1 (es) 2002-09-23 2005-03-31 3F Therapeutics Inc Valvula mitral protesica
US6814746B2 (en) 2002-11-01 2004-11-09 Ev3 Peripheral, Inc. Implant delivery system with marker interlock
US7485143B2 (en) 2002-11-15 2009-02-03 Abbott Cardiovascular Systems Inc. Apparatuses and methods for heart valve repair
US7608114B2 (en) 2002-12-02 2009-10-27 Gi Dynamics, Inc. Bariatric sleeve
US8551162B2 (en) 2002-12-20 2013-10-08 Medtronic, Inc. Biologically implantable prosthesis
US8088158B2 (en) 2002-12-20 2012-01-03 Boston Scientific Scimed, Inc. Radiopaque ePTFE medical devices
GB2398245B (en) 2003-02-06 2007-03-28 Great Ormond Street Hospital F Valve prosthesis
US7524332B2 (en) 2003-03-17 2009-04-28 Cook Incorporated Vascular valve with removable support component
US7399315B2 (en) 2003-03-18 2008-07-15 Edwards Lifescience Corporation Minimally-invasive heart valve with cusp positioners
US8088404B2 (en) 2003-03-20 2012-01-03 Medtronic Vasular, Inc. Biocompatible controlled release coatings for medical devices and related methods
US7771463B2 (en) 2003-03-26 2010-08-10 Ton Dai T Twist-down implant delivery technologies
US8118732B2 (en) 2003-04-01 2012-02-21 Boston Scientific Scimed, Inc. Force feedback control system for video endoscope
US7175656B2 (en) 2003-04-18 2007-02-13 Alexander Khairkhahan Percutaneous transcatheter heart valve replacement
US8221492B2 (en) 2003-04-24 2012-07-17 Cook Medical Technologies Artificial valve prosthesis with improved flow dynamics
DE602004023350D1 (de) 2003-04-30 2009-11-12 Medtronic Vascular Inc Perkutaneingesetzte provisorische Klappe
US8791171B2 (en) 2003-05-01 2014-07-29 Abbott Cardiovascular Systems Inc. Biodegradable coatings for implantable medical devices
US8512403B2 (en) 2003-05-20 2013-08-20 The Cleveland Clinic Foundation Annuloplasty ring with wing members for repair of a cardiac valve
US7429269B2 (en) 2003-07-08 2008-09-30 Ventor Technologies Ltd. Aortic prosthetic devices
US7201772B2 (en) 2003-07-08 2007-04-10 Ventor Technologies, Ltd. Fluid flow prosthetic device
US7621948B2 (en) 2003-07-21 2009-11-24 The Trustees Of The University Of Pennsylvania Percutaneous heart valve
WO2005011534A1 (fr) 2003-07-31 2005-02-10 Cook Incorporated Dispositifs a valvules prothetiques et procedes de fabrication de ces dispositifs
DE10342757A1 (de) 2003-09-16 2005-04-07 Campus Gmbh & Co. Kg Stent mit endständigen Verankerungselemeneten
US20050075725A1 (en) 2003-10-02 2005-04-07 Rowe Stanton J. Implantable prosthetic valve with non-laminar flow
US7604650B2 (en) 2003-10-06 2009-10-20 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US10219899B2 (en) 2004-04-23 2019-03-05 Medtronic 3F Therapeutics, Inc. Cardiac valve replacement systems
US20050096738A1 (en) 2003-10-06 2005-05-05 Cali Douglas S. Minimally invasive valve replacement system
US7556647B2 (en) 2003-10-08 2009-07-07 Arbor Surgical Technologies, Inc. Attachment device and methods of using the same
US7635382B2 (en) 2003-10-22 2009-12-22 Medtronic Vascular, Inc. Delivery system for long self-expanding stents
CA2544416A1 (fr) 2003-11-03 2005-05-12 B-Balloon Ltd. Traitement de bifurcations vasculaires
US7740656B2 (en) 2003-11-17 2010-06-22 Medtronic, Inc. Implantable heart valve prosthetic devices having intrinsically conductive polymers
AU2004305449B2 (en) 2003-12-09 2009-01-08 Gi Dynamics, Inc. Apparatus to be anchored within the gastrointestinal tract and anchoring method
US7186265B2 (en) 2003-12-10 2007-03-06 Medtronic, Inc. Prosthetic cardiac valves and systems and methods for implanting thereof
US8128681B2 (en) 2003-12-19 2012-03-06 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US7261732B2 (en) 2003-12-22 2007-08-28 Henri Justino Stent mounted valve
US20050137696A1 (en) 2003-12-23 2005-06-23 Sadra Medical Apparatus and methods for protecting against embolization during endovascular heart valve replacement
US8828078B2 (en) 2003-12-23 2014-09-09 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
EP2526899B1 (fr) 2003-12-23 2014-01-29 Sadra Medical, Inc. Valvule cardiaque repositionnable
US8951299B2 (en) 2003-12-23 2015-02-10 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US8182528B2 (en) 2003-12-23 2012-05-22 Sadra Medical, Inc. Locking heart valve anchor
US20050137691A1 (en) 2003-12-23 2005-06-23 Sadra Medical Two piece heart valve and anchor
US7824443B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Medical implant delivery and deployment tool
US7959666B2 (en) 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US9005273B2 (en) 2003-12-23 2015-04-14 Sadra Medical, Inc. Assessing the location and performance of replacement heart valves
US8246675B2 (en) 2003-12-23 2012-08-21 Laboratoires Perouse Kit for implanting in a duct
US9526609B2 (en) 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7329279B2 (en) 2003-12-23 2008-02-12 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7445631B2 (en) 2003-12-23 2008-11-04 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US20050137686A1 (en) 2003-12-23 2005-06-23 Sadra Medical, A Delaware Corporation Externally expandable heart valve anchor and method
US20120041550A1 (en) 2003-12-23 2012-02-16 Sadra Medical, Inc. Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements
PT2749254E (pt) 2003-12-23 2015-10-16 Boston Scient Scimed Inc Válvula cardíaca reposicionável
US8287584B2 (en) 2005-11-14 2012-10-16 Sadra Medical, Inc. Medical implant deployment tool
US20050137694A1 (en) 2003-12-23 2005-06-23 Haug Ulrich R. Methods and apparatus for endovascularly replacing a patient's heart valve
US20050137687A1 (en) 2003-12-23 2005-06-23 Sadra Medical Heart valve anchor and method
US7748389B2 (en) 2003-12-23 2010-07-06 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US7381219B2 (en) 2003-12-23 2008-06-03 Sadra Medical, Inc. Low profile heart valve and delivery system
US7871435B2 (en) 2004-01-23 2011-01-18 Edwards Lifesciences Corporation Anatomically approximate prosthetic mitral heart valve
US7597711B2 (en) 2004-01-26 2009-10-06 Arbor Surgical Technologies, Inc. Heart valve assembly with slidable coupling connections
EP1718246A4 (fr) 2004-02-05 2009-11-18 Childrens Medical Center Apport par catheter d'une valvule cardiaque de remplacement
FR2865926B1 (fr) 2004-02-11 2006-05-12 Perouse Laboratoires Prothese tubulaire.
US7311730B2 (en) 2004-02-13 2007-12-25 Shlomo Gabbay Support apparatus and heart valve prosthesis for sutureless implantation
US20090132035A1 (en) 2004-02-27 2009-05-21 Roth Alex T Prosthetic Heart Valves, Support Structures and Systems and Methods for Implanting the Same
ITTO20040135A1 (it) 2004-03-03 2004-06-03 Sorin Biomedica Cardio Spa Protesi valvolare cardiaca
EP2308425B2 (fr) 2004-03-11 2023-10-18 Percutaneous Cardiovascular Solutions Pty Limited Prothese de valvule cardiaque percutanee
US8349001B2 (en) 2004-04-07 2013-01-08 Medtronic, Inc. Pharmacological delivery implement for use with cardiac repair devices
WO2005099627A1 (fr) 2004-04-12 2005-10-27 Cook Incorporated Dispositif de reparation d'une endoprothese
US8012201B2 (en) 2004-05-05 2011-09-06 Direct Flow Medical, Inc. Translumenally implantable heart valve with multiple chamber formed in place support
WO2005110280A2 (fr) 2004-05-07 2005-11-24 Valentx, Inc. Dispositifs et méthodes pour arrimer un implant endolumenal gastro-intestinal
US20060095115A1 (en) 2004-05-10 2006-05-04 Youssef Bladillah Stent and method of manufacturing same
WO2005120380A1 (fr) 2004-06-07 2005-12-22 Image-Guided Neurologics, Inc. Marqueur d'alignement et capuchon protecteur
US7276078B2 (en) 2004-06-30 2007-10-02 Edwards Lifesciences Pvt Paravalvular leak detection, sealing, and prevention
US7462191B2 (en) 2004-06-30 2008-12-09 Edwards Lifesciences Pvt, Inc. Device and method for assisting in the implantation of a prosthetic valve
US7167746B2 (en) 2004-07-12 2007-01-23 Ats Medical, Inc. Anti-coagulation and demineralization system for conductive medical devices
US20140107761A1 (en) 2004-07-26 2014-04-17 Abbott Cardiovascular Systems Inc. Biodegradable stent with enhanced fracture toughness
US7919112B2 (en) 2004-08-26 2011-04-05 Pathak Holdings, Llc Implantable tissue compositions and method
US7566343B2 (en) 2004-09-02 2009-07-28 Boston Scientific Scimed, Inc. Cardiac valve, system, and method
US20060052867A1 (en) 2004-09-07 2006-03-09 Medtronic, Inc Replacement prosthetic heart valve, system and method of implant
US8961583B2 (en) 2004-09-08 2015-02-24 Cordis Corporation Optimized flex link for expandable stent
AU2005284739B2 (en) 2004-09-14 2011-02-24 Edwards Lifesciences Ag Device and method for treatment of heart valve regurgitation
EP2311433A3 (fr) 2004-10-21 2011-08-10 Genentech, Inc. Procédé pour le traitement de maladies néovasculaires intraoculaires
US7771472B2 (en) 2004-11-19 2010-08-10 Pulmonx Corporation Bronchial flow control devices and methods of use
US8562672B2 (en) 2004-11-19 2013-10-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US20060122634A1 (en) 2004-12-03 2006-06-08 Ino Takashi H Apparatus and method for delivering fasteners during valve replacement
DE102005003632A1 (de) 2005-01-20 2006-08-17 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Katheter für die transvaskuläre Implantation von Herzklappenprothesen
US8155754B2 (en) 2005-01-25 2012-04-10 Medtronic, Inc. Method for fabrication of low-polarization implantable stimulation electrode
US8731658B2 (en) 2005-01-31 2014-05-20 Physio-Control, Inc System and method for using diagnostic pulses in connection with defibrillation therapy
BRPI0608179A2 (pt) 2005-02-08 2009-11-17 B Balloon Ltd dispositivo e métodos para o tratamento de bifurcações vasculares
ITTO20050074A1 (it) 2005-02-10 2006-08-11 Sorin Biomedica Cardio Srl Protesi valvola cardiaca
US8685086B2 (en) 2006-02-18 2014-04-01 The Cleveland Clinic Foundation Apparatus and method for replacing a diseased cardiac valve
ES2558534T3 (es) 2005-02-18 2016-02-05 The Cleveland Clinic Foundation Aparato para sustituir una válvula cardíaca
US8057538B2 (en) 2005-02-18 2011-11-15 Medtronic, Inc. Valve holder
US8025694B2 (en) 2005-02-25 2011-09-27 Abbott Laboratories Vascular Enterprises Limited Modular vascular prosthesis and methods of use
US8083793B2 (en) 2005-02-28 2011-12-27 Medtronic, Inc. Two piece heart valves including multiple lobe valves and methods for implanting them
US7717955B2 (en) 2005-02-28 2010-05-18 Medtronic, Inc. Conformable prosthesis for implanting two-piece heart valves and methods for using them
ATE533520T1 (de) 2005-03-23 2011-12-15 Abbott Lab Abgabe von stark lipophilen mitteln durch medizinprodukte
US20060224232A1 (en) 2005-04-01 2006-10-05 Trivascular, Inc. Hybrid modular endovascular graft
US8062359B2 (en) 2005-04-06 2011-11-22 Edwards Lifesciences Corporation Highly flexible heart valve connecting band
US7513909B2 (en) 2005-04-08 2009-04-07 Arbor Surgical Technologies, Inc. Two-piece prosthetic valves with snap-in connection and methods for use
US7722666B2 (en) 2005-04-15 2010-05-25 Boston Scientific Scimed, Inc. Valve apparatus, system and method
EP1893131A1 (fr) 2005-04-20 2008-03-05 The Cleveland Clinic Foundation Appareil et méthode de remplacement d'une valve cardiaque
SE531468C2 (sv) 2005-04-21 2009-04-14 Edwards Lifesciences Ag En anordning för styrning av blodflöde
US20070118207A1 (en) 2005-05-04 2007-05-24 Aga Medical Corporation System for controlled delivery of stents and grafts
US7824436B2 (en) 2005-05-13 2010-11-02 Benechill, Inc. Methods and devices for non-invasive cerebral and systemic cooling
US7914569B2 (en) 2005-05-13 2011-03-29 Medtronics Corevalve Llc Heart valve prosthesis and methods of manufacture and use
CN101180010B (zh) 2005-05-24 2010-12-01 爱德华兹生命科学公司 快速展开假体心脏瓣膜
EP1895942B1 (fr) 2005-05-27 2020-05-13 Medtronic, Inc. Joint a collier pour valves cardiaques prothetiques
US7739971B2 (en) 2005-06-07 2010-06-22 Edwards Lifesciences Corporation Systems and methods for assembling components of a fabric-covered prosthetic heart valve
US8012198B2 (en) 2005-06-10 2011-09-06 Boston Scientific Scimed, Inc. Venous valve, system, and method
US7780723B2 (en) 2005-06-13 2010-08-24 Edwards Lifesciences Corporation Heart valve delivery system
US8685083B2 (en) 2005-06-27 2014-04-01 Edwards Lifesciences Corporation Apparatus, system, and method for treatment of posterior leaflet prolapse
US7776084B2 (en) 2005-07-13 2010-08-17 Edwards Lifesciences Corporation Prosthetic mitral heart valve having a contoured sewing ring
US20090112309A1 (en) 2005-07-21 2009-04-30 The Florida International University Board Of Trustees Collapsible Heart Valve with Polymer Leaflets
US8790396B2 (en) 2005-07-27 2014-07-29 Medtronic 3F Therapeutics, Inc. Methods and systems for cardiac valve delivery
US7455689B2 (en) 2005-08-25 2008-11-25 Edwards Lifesciences Corporation Four-leaflet stented mitral heart valve
WO2007024481A2 (fr) 2005-08-25 2007-03-01 Medtronic Vascular, Inc. Compositions polymeres a base de 4-aza-caprolactone utiles pour la fabrication de dispositifs medicaux biodegradables et en tant que revetements pour dispositifs medicaux
US7611534B2 (en) 2005-08-25 2009-11-03 The Cleveland Clinic Foundation Percutaneous atrioventricular valve and method of use
US7712606B2 (en) 2005-09-13 2010-05-11 Sadra Medical, Inc. Two-part package for medical implant
BRPI0616331A2 (pt) 2005-09-21 2011-06-14 Balloon Ltd B balço bifurcado e stent
US7569071B2 (en) 2005-09-21 2009-08-04 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
EP1945142B1 (fr) 2005-09-26 2013-12-25 Medtronic, Inc. Valve cardiaque prothétique et valvules veineuses
US9011528B2 (en) 2005-09-30 2015-04-21 Medtronic, Inc. Flexible annuloplasty prosthesis
US20070129794A1 (en) 2005-10-05 2007-06-07 Fidel Realyvasquez Method and apparatus for prosthesis attachment using discrete elements
US8167932B2 (en) 2005-10-18 2012-05-01 Edwards Lifesciences Corporation Heart valve delivery system with valve catheter
US7563277B2 (en) 2005-10-24 2009-07-21 Cook Incorporated Removable covering for implantable frame projections
DE102005051849B4 (de) 2005-10-28 2010-01-21 JenaValve Technology Inc., Wilmington Vorrichtung zur Implantation und Befestigung von Herzklappenprothesen
DE102005052628B4 (de) 2005-11-04 2014-06-05 Jenavalve Technology Inc. Selbstexpandierendes, flexibles Drahtgeflecht mit integrierter Klappenprothese für den transvaskulären Herzklappenersatz und ein System mit einer solchen Vorrichtung und einem Einführkatheter
AU2006315812B2 (en) 2005-11-10 2013-03-28 Cardiaq Valve Technologies, Inc. Balloon-expandable, self-expanding, vascular prosthesis connecting stent
US8764820B2 (en) 2005-11-16 2014-07-01 Edwards Lifesciences Corporation Transapical heart valve delivery system and method
US20070213813A1 (en) 2005-12-22 2007-09-13 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
RU2302220C1 (ru) 2005-12-23 2007-07-10 Александр Петрович Мельников Протез клапана сердца
TW200731980A (en) 2005-12-29 2007-09-01 Alcon Mfg Ltd RNAi-mediated inhibition of HIF1A for treatment of ocular angiogenesis
WO2007079413A2 (fr) 2005-12-30 2007-07-12 C.R. Bard Inc. Filtre pour caillots sanguins à organes de filtre revêtus biorésorbables
US8083792B2 (en) 2006-01-24 2011-12-27 Cordis Corporation Percutaneous endoprosthesis using suprarenal fixation and barbed anchors
USD553747S1 (en) 2006-01-25 2007-10-23 Cornova, Inc. Stent device
US7627376B2 (en) 2006-01-30 2009-12-01 Medtronic, Inc. Intravascular medical device
WO2007088546A2 (fr) 2006-02-02 2007-08-09 Releaf Medical Ltd. Dispositif de génération d'ondes de choc et son procédé d'utilisation tel que pour le traitement de la sténose aortique calcifiée
CN101415379B (zh) 2006-02-14 2012-06-20 萨德拉医学公司 用于输送医疗植入物的***
WO2008029296A2 (fr) 2006-02-16 2008-03-13 Endocor Pte Ltd. Remplacement d'une valvule cardiaque en une chirurgie mini-invasive
US8403981B2 (en) * 2006-02-27 2013-03-26 CardiacMC, Inc. Methods and devices for delivery of prosthetic heart valves and other prosthetics
US7910152B2 (en) 2006-02-28 2011-03-22 Advanced Cardiovascular Systems, Inc. Poly(ester amide)-based drug delivery systems with controlled release rate and morphology
US8219229B2 (en) 2006-03-02 2012-07-10 Edwards Lifesciences Corporation Virtual heart valve
US8043673B2 (en) 2006-03-02 2011-10-25 Boston Scientific Scimed, Inc. Method to make tube-in-tube balloon
JP5102279B2 (ja) 2006-03-10 2012-12-19 メドトロニック，インコーポレイテッド 人工弁イントロデューサ並びにその製造方法及びその使用方法
EP2004095B1 (fr) 2006-03-28 2019-06-12 Medtronic, Inc. Valvule cardiaque prothétique constituée de matière péricardique et procédés de production de cette valvule
RU2325874C2 (ru) 2006-04-04 2008-06-10 Александр Васильевич Самков Протез клапана сердца
US8551161B2 (en) 2006-04-25 2013-10-08 Medtronic Vascular, Inc. Cardiac valve annulus restraining device
US8652201B2 (en) 2006-04-26 2014-02-18 The Cleveland Clinic Foundation Apparatus and method for treating cardiovascular diseases
EP2023859B1 (fr) 2006-04-28 2012-12-26 Medtronic, Inc. Appareil pour remplacer une valve cardiaque
WO2007130881A2 (fr) 2006-04-29 2007-11-15 Arbor Surgical Technologies, Inc. Ensembles de valves cardiaques prosthétiques à composants multiples et appareil et procédés pour leur implantation
EP2012712B1 (fr) 2006-04-29 2016-02-10 Medtronic, Inc. Guides pour des valves cardiaques prosthétiques à composants multiples
EP2015709B1 (fr) 2006-05-05 2013-01-09 Children's Medical Center Corporation Prothèses de valvules cardiaques par cathéter
GB2437921B (en) 2006-05-10 2011-08-03 Francis Wells Heart valve repair
EP2353553B1 (fr) 2006-05-12 2015-12-02 Covidien LP Implant et système de distribution doté de plusieurs verrouillages de marqueur
US8986713B2 (en) 2006-05-12 2015-03-24 W. L. Gore & Associates, Inc. Medical device capable of being compacted and expanded having anti-thrombin III binding activity
US8142495B2 (en) 2006-05-15 2012-03-27 Edwards Lifesciences Ag System and a method for altering the geometry of the heart
FR2901146A1 (fr) 2006-05-18 2007-11-23 Ela Medical Soc Par Actions Si Dispositif medical implantable actif de stimulation cardiaque, resynchronisation, cardioversion et/ou defibrillation, comportant des moyens de detection d'artefacts de bruit ventriculaire
US8753384B2 (en) 2006-05-19 2014-06-17 Boston Scientific Scimed, Inc. Apparatus and method for loading and delivering a stent
US8535368B2 (en) 2006-05-19 2013-09-17 Boston Scientific Scimed, Inc. Apparatus for loading and delivering a stent
US20090270972A1 (en) 2006-05-23 2009-10-29 All-Vascular Pty Ltd. Endovenous valve transfer stent
US7959940B2 (en) 2006-05-30 2011-06-14 Advanced Cardiovascular Systems, Inc. Polymer-bioceramic composite implantable medical devices
CN101484093B (zh) 2006-06-01 2011-09-07 爱德华兹生命科学公司 用于改善心瓣膜功能的人工***物
WO2007138571A2 (fr) 2006-06-01 2007-12-06 Mor Research Applications Ltd. Augmentation de la membrane, notamment pour le traitement de valvules cardiaques et dispositifs de fixation pour l'augmentation de la membrane
CA2653190C (fr) 2006-06-06 2015-07-14 Cook Incorporated Stent avec zone resistant a l'ecrasement
US8778376B2 (en) 2006-06-09 2014-07-15 Advanced Cardiovascular Systems, Inc. Copolymer comprising elastin pentapeptide block and hydrophilic block, and medical device and method of treating
US8114150B2 (en) 2006-06-14 2012-02-14 Advanced Cardiovascular Systems, Inc. RGD peptide attached to bioabsorbable stents
AU2007260951A1 (en) 2006-06-21 2007-12-27 Aortx, Inc. Prosthetic valve implantation systems
DE102006028533A1 (de) 2006-06-21 2008-01-03 Iprm Intellectual Property Rights Management Ag Vorrichtung und Computerprogramm zum Bestimmen eines Lungenzustands eines Patienten, welcher durch ein kardiopulmonales Blutvolumen dargestellt wird
US8128688B2 (en) 2006-06-27 2012-03-06 Abbott Cardiovascular Systems Inc. Carbon coating on an implantable device
US8449605B2 (en) 2006-06-28 2013-05-28 Kardium Inc. Method for anchoring a mitral valve
US20080077231A1 (en) 2006-07-06 2008-03-27 Prescient Medical, Inc. Expandable vascular endoluminal prostheses
EP2037848A1 (fr) 2006-07-07 2009-03-25 Boston Scientific Limited Système d'acheminement d'endoprothèse à support de prothèse
US8685430B1 (en) 2006-07-14 2014-04-01 Abbott Cardiovascular Systems Inc. Tailored aliphatic polyesters for stent coatings
US20080021546A1 (en) 2006-07-18 2008-01-24 Tim Patz System for deploying balloon-expandable heart valves
US20090306768A1 (en) 2006-07-28 2009-12-10 Cardiaq Valve Technologies, Inc. Percutaneous valve prosthesis and system and method for implanting same
GB2440809B (en) 2006-07-28 2011-08-10 Geoffrey Douglas Tansley Improved heart valve prosthesis
US8454684B2 (en) 2006-08-02 2013-06-04 Medtronic, Inc. Heart valve holder for use in valve implantation procedures
US7871432B2 (en) 2006-08-02 2011-01-18 Medtronic, Inc. Heart valve holder for use in valve implantation procedures
JP4682259B2 (ja) 2006-09-08 2011-05-11 エドワーズ ライフサイエンシーズ コーポレイション 一体型心臓弁送達システム
US20100179647A1 (en) 2006-09-11 2010-07-15 Carpenter Judith T Methods of reducing embolism to cerebral circulation as a consequence of an index cardiac procedure
US8460335B2 (en) 2006-09-11 2013-06-11 Embrella Cardiovascular, Inc. Method of deflecting emboli from the cerebral circulation
US8834564B2 (en) 2006-09-19 2014-09-16 Medtronic, Inc. Sinus-engaging valve fixation member
US8876894B2 (en) 2006-09-19 2014-11-04 Medtronic Ventor Technologies Ltd. Leaflet-sensitive valve fixation member
FR2906454B1 (fr) 2006-09-28 2009-04-10 Perouse Soc Par Actions Simpli Implant destine a etre place dans un conduit de circulation du sang.
CA2664662A1 (fr) 2006-09-28 2008-04-03 Heart Leaflet Technologies, Inc. Outil d'installation pour installation percutanee d'une prothese
US7534261B2 (en) 2006-10-02 2009-05-19 Edwards Lifesciences Corporation Sutureless heart valve attachment
US8029556B2 (en) 2006-10-04 2011-10-04 Edwards Lifesciences Corporation Method and apparatus for reshaping a ventricle
US8784478B2 (en) 2006-10-16 2014-07-22 Medtronic Corevalve, Inc. Transapical delivery system with ventruculo-arterial overlfow bypass
US20080097571A1 (en) 2006-10-21 2008-04-24 Paragon Intellectual Properties, Llc Deformable lumen support devices and methods of use
CA2666485C (fr) 2006-10-27 2015-10-06 Edwards Lifesciences Corporation Tissu biologique pour implantation chirurgicale
DE102006052564B3 (de) 2006-11-06 2007-12-13 Georg Lutter Mitralklappenstent
AU2007317777B2 (en) 2006-11-07 2012-08-02 Cook Incorporated Fenestrations for stent graft arrangements and stent graft including the same
AU2007317191B2 (en) 2006-11-07 2014-02-20 Corvia Medical, Inc. Devices and methods for the treatment of heart failure
US7615072B2 (en) 2006-11-14 2009-11-10 Medtronic Vascular, Inc. Endoluminal prosthesis
JP5593545B2 (ja) 2006-12-06 2014-09-24 メドトロニック シーブイ ルクセンブルク エス．アー．エール．エル． 弁輪に固定された自己拡張型弁の経心尖的送達のためのシステムおよび方法
FR2909857B1 (fr) 2006-12-14 2009-03-06 Perouse Soc Par Actions Simpli Endovalve.
US8070799B2 (en) 2006-12-19 2011-12-06 Sorin Biomedica Cardio S.R.L. Instrument and method for in situ deployment of cardiac valve prostheses
WO2008079272A2 (fr) 2006-12-19 2008-07-03 St. Jude Medical, Inc. Valvule cardiaque prothétique comprenant une structure de stent et des feuillets de tissu, et procédés apparentés
US8470024B2 (en) 2006-12-19 2013-06-25 Sorin Group Italia S.R.L. Device for in situ positioning of cardiac valve prosthesis
US8236045B2 (en) 2006-12-22 2012-08-07 Edwards Lifesciences Corporation Implantable prosthetic valve assembly and method of making the same
EP2444031B1 (fr) 2007-01-19 2015-07-15 Medtronic, Inc. Dispositif de mise en place d'endoprothèse
WO2008089365A2 (fr) 2007-01-19 2008-07-24 The Cleveland Clinic Foundation Méthode de mise en place d'une valve cardiovasculaire
WO2008097589A1 (fr) 2007-02-05 2008-08-14 Boston Scientific Limited Valve percutanée, système et procédé
US20080319526A1 (en) 2007-02-05 2008-12-25 Hill Jason P Percutaneous valve, system and method
WO2008101113A1 (fr) 2007-02-14 2008-08-21 Edwards Lifesciences Corporation Suture et procédé destinés à réparer le cœur
WO2008100600A1 (fr) 2007-02-16 2008-08-21 Medtronic, Inc. Valvules cardiaques prothétiques de remplacement, et procédés d'implantation
US7753949B2 (en) 2007-02-23 2010-07-13 The Trustees Of The University Of Pennsylvania Valve prosthesis systems and methods
US8070802B2 (en) 2007-02-23 2011-12-06 The Trustees Of The University Of Pennsylvania Mitral valve system
US8303622B2 (en) 2007-03-14 2012-11-06 St. Jude Medical, Inc. Heart valve chordae replacement methods and apparatus
US8653632B2 (en) 2007-03-28 2014-02-18 Medtronic Ats Medical Inc. System and method for conditioning implantable medical devices
US9138315B2 (en) 2007-04-13 2015-09-22 Jenavalve Technology Gmbh Medical device for treating a heart valve insufficiency or stenosis
WO2008125145A1 (fr) 2007-04-13 2008-10-23 Synergio Ag Dispositif et procédé de pénétration tissulaire
US7896915B2 (en) 2007-04-13 2011-03-01 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US7806917B2 (en) 2007-04-17 2010-10-05 Medtronic Vascular, Inc. Stent graft fixation system and method
EP2155319B1 (fr) 2007-04-20 2018-08-08 Medtronic, Inc. Ensemble fil et connecteur électrique médical implantable
US20080262603A1 (en) 2007-04-23 2008-10-23 Sorin Biomedica Cardio Prosthetic heart valve holder
JP5264264B2 (ja) 2007-04-23 2013-08-14 セント ジョセフズ トランスレーショナル リサーチ インスティテュート インコーポレイテッド 交換用心臓弁およびその製造方法
US8409274B2 (en) 2007-04-26 2013-04-02 St. Jude Medical, Inc. Techniques for attaching flexible leaflets of prosthetic heart valves to supporting structures
US8147504B2 (en) 2007-05-05 2012-04-03 Medtronic, Inc. Apparatus and methods for delivering fasteners during valve replacement
US8480730B2 (en) 2007-05-14 2013-07-09 Cardiosolutions, Inc. Solid construct mitral spacer
US9572660B2 (en) 2007-06-04 2017-02-21 St. Jude Medical, Inc. Prosthetic heart valves
US8425591B1 (en) 2007-06-11 2013-04-23 Abbott Cardiovascular Systems Inc. Methods of forming polymer-bioceramic composite medical devices with bioceramic particles
EP2160150B1 (fr) 2007-06-26 2011-10-26 St. Jude Medical, Inc. Appareil d'implantation de valvules cardiaques prosthétiques repliable/expansibles
US8006535B2 (en) 2007-07-12 2011-08-30 Sorin Biomedica Cardio S.R.L. Expandable prosthetic valve crimping device
US8852620B2 (en) 2007-07-20 2014-10-07 Medtronic Vascular, Inc. Medical devices comprising polymeric drug delivery systems with drug solubility gradients
US8663319B2 (en) 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Methods and apparatus for percutaneous aortic valve replacement
US8663318B2 (en) 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Method and apparatus for percutaneous aortic valve replacement
US8828079B2 (en) 2007-07-26 2014-09-09 Boston Scientific Scimed, Inc. Circulatory valve, system and method
US8182829B2 (en) 2007-07-27 2012-05-22 Abbott Cardiovascular Systems Inc. Drug eluting implantable medical device with hemocompatible and/or prohealing topcoat
US8961589B2 (en) 2007-08-01 2015-02-24 Abbott Cardiovascular Systems Inc. Bioabsorbable coating with tunable hydrophobicity
US8747458B2 (en) 2007-08-20 2014-06-10 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
ES2632485T3 (es) 2007-08-21 2017-09-13 Symetis Sa Una válvula de reemplazo
JP5329542B2 (ja) 2007-08-23 2013-10-30 ダイレクト フロウ メディカル、 インク． インプレース形成支持部を有する経腔的に移植可能な心臓弁
ES2384199T3 (es) 2007-08-24 2012-07-02 St. Jude Medical, Inc. Válvulas cardiacas aórticas protésicas
US20090093876A1 (en) 2007-08-31 2009-04-09 Edwards Lifesciences Corporation Recoil inhibitor for prosthetic valve
US8114154B2 (en) 2007-09-07 2012-02-14 Sorin Biomedica Cardio S.R.L. Fluid-filled delivery system for in situ deployment of cardiac valve prostheses
US8906081B2 (en) 2007-09-13 2014-12-09 W. L. Gore & Associates, Inc. Stented vascular graft
DE102007043830A1 (de) 2007-09-13 2009-04-02 Lozonschi, Lucian, Madison Herzklappenstent
US8220121B2 (en) 2007-09-14 2012-07-17 Cook Medical Technologies Llc Device for loading a self-expandable prosthesis into a sheath
US8273118B2 (en) 2007-09-17 2012-09-25 Medtronic, Inc. Heart valve holder assembly for use in valve implantation procedures
US20090076531A1 (en) 2007-09-18 2009-03-19 Richardson Charles L Method and apparatus for bypass graft
US8066755B2 (en) 2007-09-26 2011-11-29 Trivascular, Inc. System and method of pivoted stent deployment
US20090082847A1 (en) 2007-09-26 2009-03-26 Boston Scientific Corporation System and method of securing stent barbs
WO2009045334A1 (fr) 2007-09-28 2009-04-09 St. Jude Medical, Inc. Valvules cardiaques prothétiques repliables/déployables dotées de caractéristiques de retenue des valves natives calcifiées
US8998978B2 (en) 2007-09-28 2015-04-07 Abbott Cardiovascular Systems Inc. Stent formed from bioerodible metal-bioceramic composite
WO2009045331A1 (fr) 2007-09-28 2009-04-09 St. Jude Medical, Inc. Valvules cardiaques prothétiques repliables/déployables en deux temps et systèmes d'ancrage
US8180428B2 (en) 2007-10-03 2012-05-15 Medtronic, Inc. Methods and systems for use in selecting cardiac pacing sites
US9040646B2 (en) 2007-10-04 2015-05-26 W. L. Gore & Associates, Inc. Expandable TFE copolymers, methods of making, and porous, expanded articles thereof
US20090138079A1 (en) 2007-10-10 2009-05-28 Vector Technologies Ltd. Prosthetic heart valve for transfemoral delivery
CA2702672C (fr) 2007-10-15 2016-03-15 Edwards Lifesciences Corporation Valvule cardiaque transcatheter pourvue de microdispositifs d'ancrage
WO2009055286A1 (fr) 2007-10-24 2009-04-30 Edwards Lifesciences Corporation Dispositif d'extraction percutanée de stent en nitinol
WO2009053497A1 (fr) 2007-10-25 2009-04-30 Symetis Sa Stents, stents à valve et procédés et systèmes de mise en place de ceux-ci
US8009887B2 (en) 2007-11-02 2011-08-30 Siemens Corporation Method and system for automatic quantification of aortic valve function from 4D computed tomography data using a physiological model
ES2380555T3 (es) 2007-11-05 2012-05-16 St. Jude Medical, Inc. Válvulas protésicas del corazón plegables/expansibles con soportes de stent no expansible y características de recuperación
US8715337B2 (en) 2007-11-09 2014-05-06 Cook Medical Technologies Llc Aortic valve stent graft
US20090125096A1 (en) 2007-11-12 2009-05-14 Medtronic Vascular, Inc. Stent Graft With Pins
US20090148491A1 (en) 2007-12-05 2009-06-11 Abbott Cardiovascular Systems Inc. Dual-Targeted Drug Carriers
US20090149946A1 (en) 2007-12-05 2009-06-11 Cook Incorporated Stent having at least one barb and methods of manufacture
ES2897664T3 (es) 2007-12-14 2022-03-02 Edwards Lifesciences Corp Armazón de unión de valvas para una válvula protésica
US8357387B2 (en) 2007-12-21 2013-01-22 Edwards Lifesciences Corporation Capping bioprosthetic tissue to reduce calcification
US9370437B2 (en) 2007-12-26 2016-06-21 Cook Medical Technologies Llc Stent having less invasive ends
US20090171456A1 (en) 2007-12-28 2009-07-02 Kveen Graig L Percutaneous heart valve, system, and method
US8926688B2 (en) 2008-01-11 2015-01-06 W. L. Gore & Assoc. Inc. Stent having adjacent elements connected by flexible webs
EP2252240B1 (fr) 2008-01-14 2012-08-01 Boston Scientific Scimed, Inc. Appareil de relachement de suture de type clamp et procede de chargement et d'acheminement de stent
WO2009091509A1 (fr) 2008-01-16 2009-07-23 St. Jude Medical, Inc. Système de mise en place et de retrait de valvules cardiaques prothétiques repliables/expansibles
US9364324B2 (en) 2008-01-24 2016-06-14 Medtronic Vascular, Inc. Infundibular reducer device delivery system and related methods
WO2009094197A1 (fr) 2008-01-24 2009-07-30 Medtronic, Inc. Stents pour valvules cardiaques prothétiques
US8157852B2 (en) 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
DK2254514T3 (en) 2008-01-24 2018-12-17 Medtronic Inc STENTS FOR HEART VALVE PROSTHESIS
US7993395B2 (en) 2008-01-25 2011-08-09 Medtronic, Inc. Set of annuloplasty devices with varying anterior-posterior ratios and related methods
US8801776B2 (en) 2008-02-25 2014-08-12 Medtronic Vascular, Inc. Infundibular reducer devices
US8465540B2 (en) 2008-02-26 2013-06-18 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis
EP3005984A1 (fr) 2008-02-28 2016-04-13 Medtronic Inc. Systèmes de prothèse de valve cardiaque
US8968393B2 (en) 2008-02-28 2015-03-03 Medtronic, Inc. System and method for percutaneous mitral valve repair
WO2009108942A1 (fr) 2008-02-29 2009-09-03 Edwards Lifesciences Corporation Elément extensible servant à déployer une prothèse
US8177836B2 (en) 2008-03-10 2012-05-15 Medtronic, Inc. Apparatus and methods for minimally invasive valve repair
US8313525B2 (en) 2008-03-18 2012-11-20 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
US8377116B2 (en) 2008-03-20 2013-02-19 Abbott Cardiovascular Systems Inc. Implantable medical device coatings with improved mechanical stability
US7815673B2 (en) 2008-04-01 2010-10-19 Medtronic Vascular, Inc. Double-walled stent system
US8430927B2 (en) 2008-04-08 2013-04-30 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
WO2009126629A1 (fr) 2008-04-09 2009-10-15 Georgia Tech Research Corporation Anneaux d'annuloplastie et procédés de réparation de valvule cardiaque
US8480731B2 (en) 2008-04-14 2013-07-09 Medtronic ATS Medical, Inc. Tool for implantation of replacement heart valve
FR2930137B1 (fr) 2008-04-18 2010-04-23 Corevalve Inc Materiel de traitement d'une valve cardiaque, en particulier d'une valve mitrale.
US8312825B2 (en) 2008-04-23 2012-11-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
AU2009240565B2 (en) 2008-04-23 2013-08-22 Medtronic, Inc. Stented heart valve devices
US8696743B2 (en) 2008-04-23 2014-04-15 Medtronic, Inc. Tissue attachment devices and methods for prosthetic heart valves
US8323336B2 (en) 2008-04-23 2012-12-04 Medtronic, Inc. Prosthetic heart valve devices and methods of valve replacement
US8136218B2 (en) 2008-04-29 2012-03-20 Medtronic, Inc. Prosthetic heart valve, prosthetic heart valve assembly and method for making same
US20090276040A1 (en) 2008-05-01 2009-11-05 Edwards Lifesciences Corporation Device and method for replacing mitral valve
US9061119B2 (en) 2008-05-09 2015-06-23 Edwards Lifesciences Corporation Low profile delivery system for transcatheter heart valve
ATE554731T1 (de) 2008-05-16 2012-05-15 Sorin Biomedica Cardio Srl Atraumatische prothetische herzklappenprothese
US8202529B2 (en) 2008-05-30 2012-06-19 Abbott Cardiovascular Systems Inc. Implantable drug delivery devices having alternating hydrophilic and amphiphilic polymer layers
CA3063780C (fr) 2008-06-06 2021-12-14 Edwards Lifesciences Corporation Valvule cardiaque transcatheter de faible profil
US20110160836A1 (en) 2008-06-20 2011-06-30 Vysera Biomedical Limited Valve device
US8323335B2 (en) 2008-06-20 2012-12-04 Edwards Lifesciences Corporation Retaining mechanisms for prosthetic valves and methods for using
US20100121461A1 (en) 2008-06-20 2010-05-13 Vysera Biomedical Limited Valve
EP3520737B1 (fr) 2008-07-15 2023-05-10 St. Jude Medical, LLC Modèles de collerette pour valve cardiaque prothétique repliable et redéployable et applications techniques complémentaires
EP2331016B8 (fr) 2008-07-15 2020-06-03 St. Jude Medical, LLC Ancrage axial pliable et redéployable de valvule cardiaque prothétique pour divers états de maladie
PL2334227T3 (pl) 2008-09-11 2022-09-12 Acist Medical Systems, Inc. Urządzenie dostarczające czujnik fizjologiczny i układ do iniekcji płynu
WO2010031082A2 (fr) 2008-09-15 2010-03-18 Arbor Surgical Technologies, Inc. Outils, systèmes et procédés de remodelage de tissu
WO2010031060A1 (fr) 2008-09-15 2010-03-18 Medtronic Ventor Technologies Ltd. Valvule cardiaque prosthétique ayant des identifiants pour faciliter le positionnement radiographique
US8721714B2 (en) 2008-09-17 2014-05-13 Medtronic Corevalve Llc Delivery system for deployment of medical devices
US9314335B2 (en) 2008-09-19 2016-04-19 Edwards Lifesciences Corporation Prosthetic heart valve configured to receive a percutaneous prosthetic heart valve implantation
US8287591B2 (en) 2008-09-19 2012-10-16 Edwards Lifesciences Corporation Transformable annuloplasty ring configured to receive a percutaneous prosthetic heart valve implantation
EP2367505B1 (fr) 2008-09-29 2020-08-12 Edwards Lifesciences CardiAQ LLC Valvule cardiaque
WO2010040009A1 (fr) 2008-10-01 2010-04-08 Cardiaq Valve Technologies, Inc. Système de mise en place pour implant vasculaire
US8790387B2 (en) 2008-10-10 2014-07-29 Edwards Lifesciences Corporation Expandable sheath for introducing an endovascular delivery device into a body
US8690936B2 (en) 2008-10-10 2014-04-08 Edwards Lifesciences Corporation Expandable sheath for introducing an endovascular delivery device into a body
US8137398B2 (en) 2008-10-13 2012-03-20 Medtronic Ventor Technologies Ltd Prosthetic valve having tapered tip when compressed for delivery
US8449625B2 (en) 2009-10-27 2013-05-28 Edwards Lifesciences Corporation Methods of measuring heart valve annuluses for valve replacement
US20100114305A1 (en) 2008-10-30 2010-05-06 Wei-Chang Kang Implantable Valvular Prosthesis
WO2010057262A1 (fr) 2008-11-21 2010-05-27 Percutaneous Cardiovascular Solutions Pty Limited Prothèse de valve cardiaque et procédé
EP2358302B1 (fr) 2008-12-18 2012-12-05 Cook Medical Technologies LLC Stents et greffes de stent
US8308798B2 (en) 2008-12-19 2012-11-13 Edwards Lifesciences Corporation Quick-connect prosthetic heart valve and methods
US8158187B2 (en) 2008-12-19 2012-04-17 Medtronic Vascular, Inc. Dry diazeniumdiolation methods for producing nitric oxide releasing medical devices
US8834563B2 (en) 2008-12-23 2014-09-16 Sorin Group Italia S.R.L. Expandable prosthetic valve having anchoring appendages
AU325342S (en) 2009-01-08 2009-03-25 Kk Kyoto Iryo Sekkei Stent
AU325341S (en) 2009-01-08 2009-03-25 Kk Kyoto Iryo Sekkei Stent
GB0902339D0 (en) 2009-02-12 2009-04-01 St Georges Healthcare Nhs Trus Percutaneous guidewire
US20100217382A1 (en) 2009-02-25 2010-08-26 Edwards Lifesciences Mitral valve replacement with atrial anchoring
US8740930B2 (en) 2009-02-25 2014-06-03 Medtronic Vascular, Inc. Embolic filter device independent of treatment device
AU2010218384B2 (en) 2009-02-27 2014-11-20 St. Jude Medical, Inc. Stent features for collapsible prosthetic heart valves
USD635262S1 (en) 2009-03-12 2011-03-29 Biocore Biotechnologia S/A Stent
US8021420B2 (en) 2009-03-12 2011-09-20 Medtronic Vascular, Inc. Prosthetic valve delivery system
USD635261S1 (en) 2009-03-12 2011-03-29 Biocore Biotechnologia S/A Stent
US20100233266A1 (en) 2009-03-13 2010-09-16 Cleek Robert L Articles and methods of treating vascular conditions
JP2012520716A (ja) 2009-03-17 2012-09-10 ミトラシスト メディカル リミテッド 折りたためる弁を持つ人工弁及びその送出方法
US8715207B2 (en) 2009-03-19 2014-05-06 Sorin Group Italia S.R.L. Universal valve annulus sizing device
ES2543460T3 (es) 2009-03-26 2015-08-19 Sorin Group Usa, Inc. Dispositivos de dimensionamiento de anuloplastia para intervenciones mínimamente invasivas
CN101919753A (zh) 2009-03-30 2010-12-22 卡迪万蒂奇医药公司 人工主动脉瓣膜或二尖瓣膜的无缝合移植方法和装置
US9980818B2 (en) 2009-03-31 2018-05-29 Edwards Lifesciences Corporation Prosthetic heart valve system with positioning markers
US20100256723A1 (en) 2009-04-03 2010-10-07 Medtronic Vascular, Inc. Prosthetic Valve With Device for Restricting Expansion
US8414644B2 (en) 2009-04-15 2013-04-09 Cardiaq Valve Technologies, Inc. Vascular implant and delivery system
US8500688B2 (en) 2009-04-16 2013-08-06 Medtronic, Inc. Retrograde coronary sinus perfusion cannula and methods of using same
US8500801B2 (en) 2009-04-21 2013-08-06 Medtronic, Inc. Stents for prosthetic heart valves and methods of making same
US8734484B2 (en) 2009-04-21 2014-05-27 Medtronic, Inc. System and method for closure of an internal opening in tissue, such as a trans-apical access opening
US8876883B2 (en) 2009-04-24 2014-11-04 Medtronic Vascular, Inc. Self-flaring active fixation element for a stent graft
US9011524B2 (en) 2009-04-24 2015-04-21 Medtronic, Inc. Prosthetic heart valves and methods of attaching same
ES2523218T3 (es) 2009-04-27 2014-11-24 Sorin Group Italia S.R.L. Conducto vascular protésico
EP2424428B1 (fr) 2009-04-29 2015-03-04 St. Jude Medical AB Dispositif de surveillance de perfusion coronaire implantable
NZ596179A (en) 2009-04-29 2014-05-30 Cleveland Clinic Foundation Apparatus and method for replacing a diseased cardiac valve
US8353953B2 (en) 2009-05-13 2013-01-15 Sorin Biomedica Cardio, S.R.L. Device for the in situ delivery of heart valves
US8449466B2 (en) 2009-05-28 2013-05-28 Edwards Lifesciences Corporation System and method for locating medical devices in vivo using ultrasound Doppler mode
US8075611B2 (en) 2009-06-02 2011-12-13 Medtronic, Inc. Stented prosthetic heart valves
US8348998B2 (en) 2009-06-26 2013-01-08 Edwards Lifesciences Corporation Unitary quick connect prosthetic heart valve and deployment system and methods
US8475522B2 (en) 2009-07-14 2013-07-02 Edwards Lifesciences Corporation Transapical delivery system for heart valves
US8821570B2 (en) 2009-07-20 2014-09-02 Micardia Corporation Adjustable annuloplasty ring with subcutaneous activation port
US8119704B2 (en) 2009-07-21 2012-02-21 Abbott Cardiovascular Systems Inc. Implantable medical device comprising copolymer of L-lactide with improved fracture toughness
US20110022165A1 (en) 2009-07-23 2011-01-27 Edwards Lifesciences Corporation Introducer for prosthetic heart valve
US8876712B2 (en) 2009-07-29 2014-11-04 Edwards Lifesciences Corporation Intracardiac sheath stabilizer
EP3150215A1 (fr) 2009-08-24 2017-04-05 Stealth Peptides International, Inc. Procédés et compositions pour la prévention ou le traitement d'affections ophtalmiques
WO2011025945A1 (fr) 2009-08-27 2011-03-03 Medtronic Inc. Systèmes et procédés de pose de valve par transcathéter
US8545742B2 (en) 2009-08-28 2013-10-01 Abbott Cardiovascular Systems Inc. Method of fabricating a low crystallinity poly(L-lactide) tube
CA2772344C (fr) 2009-08-28 2018-05-01 3F Therapeutics, Inc. Dispositif de sertissage et son procede d'utilisation
US9757107B2 (en) 2009-09-04 2017-09-12 Corvia Medical, Inc. Methods and devices for intra-atrial shunts having adjustable sizes
WO2011031733A2 (fr) 2009-09-09 2011-03-17 The Cleveland Clinic Foundation Appareil et procédé pour distribuer un dispositif médical implantable au niveau d'une valve cardiaque malade
EP2633821B1 (fr) 2009-09-15 2016-04-06 Evalve, Inc. Dispositif de réparation de valve cardiaque
WO2011035154A1 (fr) 2009-09-18 2011-03-24 The Regents Of The University Of California Remplacement de valvule cardiaque prothetique endovasculaire
WO2011035327A1 (fr) 2009-09-21 2011-03-24 Medtronic Inc. Système et procédé de pose de valvule cardiaque prothétique de type transcathéter à stent
WO2011038353A2 (fr) 2009-09-28 2011-03-31 Ryan Timothy J Greffes chargées et leurs procédés d'utilisation
US9730790B2 (en) 2009-09-29 2017-08-15 Edwards Lifesciences Cardiaq Llc Replacement valve and method
CN107260367B (zh) 2009-11-02 2019-11-29 西美蒂斯股份公司 主动脉生物假体及用于其递送的***
US8449599B2 (en) 2009-12-04 2013-05-28 Edwards Lifesciences Corporation Prosthetic valve for replacing mitral valve
HUE059497T2 (hu) 2010-03-05 2022-11-28 Edwards Lifesciences Corp Tartószerkezetek szívbillentyû-protézis számára
US8795354B2 (en) 2010-03-05 2014-08-05 Edwards Lifesciences Corporation Low-profile heart valve and delivery system
US8623079B2 (en) 2010-04-23 2014-01-07 Medtronic, Inc. Stents for prosthetic heart valves
IT1400544B1 (it) 2010-06-09 2013-06-11 Sorin Biomedica Cardio Srl Procedimento di detossificazione di tessuto biologico.
CA2803149C (fr) 2010-06-21 2018-08-14 Impala, Inc. Prothese de valvule cardiaque
EP2608743B1 (fr) 2010-08-24 2018-04-04 Edwards Lifesciences Corporation Anneau d'annuloplastie souple comprenant des points de contrôle sélectionnés
WO2012040655A2 (fr) 2010-09-23 2012-03-29 Cardiaq Valve Technologies, Inc. Valvules prothétiques, dispositifs de pose et procédés afférents
US9393110B2 (en) 2010-10-05 2016-07-19 Edwards Lifesciences Corporation Prosthetic heart valve
JP2013542773A (ja) 2010-10-08 2013-11-28 エドワーズ ライフサイエンシーズ コーポレイション 総ヘモグロビンの連続測定
US8945209B2 (en) 2011-05-20 2015-02-03 Edwards Lifesciences Corporation Encapsulated heart valve
WO2012175483A1 (fr) 2011-06-20 2012-12-27 Jacques Seguin Ensemble de prothèses valvaires pour réparer une valvule cardiaque défectueuse et ses procédés d'utilisation
US9039757B2 (en) 2011-10-19 2015-05-26 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
CN104114127B (zh) 2011-12-09 2017-09-05 爱德华兹生命科学公司 具有改良的连合支撑的人工心脏瓣膜
CA2862856C (fr) 2012-01-25 2018-03-13 Intact Vascular, Inc. Dispositif endoluminal et procede associe
US9023098B2 (en) 2012-03-28 2015-05-05 Medtronic, Inc. Dual valve prosthesis for transcatheter valve implantation
US20130325121A1 (en) 2012-05-31 2013-12-05 Clemson University Protein based materials, plastic albumin devices and related methods
US9023099B2 (en) 2012-10-31 2015-05-05 Medtronic Vascular Galway Limited Prosthetic mitral valve and delivery method
US9675451B2 (en) 2013-02-01 2017-06-13 Medtronic CV Luxembourg S.a.r.l. Anti-paravalvular leakage component for a transcatheter valve prosthesis
US20140277427A1 (en) 2013-03-14 2014-09-18 Cardiaq Valve Technologies, Inc. Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
US9730791B2 (en) 2013-03-14 2017-08-15 Edwards Lifesciences Cardiaq Llc Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
US9681951B2 (en) 2013-03-14 2017-06-20 Edwards Lifesciences Cardiaq Llc Prosthesis with outer skirt and anchors
EP3016595B1 (fr) 2013-07-26 2018-12-19 Edwards Lifesciences CardiAQ LLC Systèmes pour sceller des ouvertures dans une paroi anatomique
CA2938614C (fr) 2014-02-21 2024-01-23 Edwards Lifesciences Cardiaq Llc Dispositif d'acheminement pour le deploiement maitrise d'une de valvule de substitution

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2245495A (en) * 1990-05-11 1992-01-08 John Stanley Webber Artery support insertion instrument
US5411552A (en) 1990-05-18 1995-05-02 Andersen; Henning R. Valve prothesis for implantation in the body and a catheter for implanting such valve prothesis
US6251093B1 (en) * 1991-07-16 2001-06-26 Heartport, Inc. Methods and apparatus for anchoring an occluding member
US6168616B1 (en) * 1997-06-02 2001-01-02 Global Vascular Concepts Manually expandable stent
US6830584B1 (en) 1999-11-17 2004-12-14 Jacques Seguin Device for replacing a cardiac valve by percutaneous route
US20050283231A1 (en) * 2004-06-16 2005-12-22 Haug Ulrich R Everting heart valve
US20070250151A1 (en) * 2006-04-24 2007-10-25 Scimed Life Systems, Inc. Endovascular aortic repair delivery system with anchor

Also Published As

Publication number Publication date
US20130110227A1 (en) 2013-05-02
CA2739275C (fr) 2017-01-17
EP2341871A1 (fr) 2011-07-13
US20100082089A1 (en) 2010-04-01
CA2739275A1 (fr) 2010-04-08
US20150081009A1 (en) 2015-03-19
US9744039B2 (en) 2017-08-29
US20160135948A1 (en) 2016-05-19
EP2341871B1 (fr) 2017-03-22
US8337541B2 (en) 2012-12-25
US8911455B2 (en) 2014-12-16
US9597183B2 (en) 2017-03-21
WO2010040009A1 (fr) 2010-04-08

Similar Documents

Publication Publication Date Title
US9744039B2 (en) Delivery system for vascular implant
US11801138B2 (en) Suture deployment of prosthetic heart valve
US11918461B2 (en) Methods for treating a deficient native mitral valve
US11103347B2 (en) Magnetic retaining mechanisms for prosthetic valves
EP2303190B1 (fr) Mécanismes de retenue de valves prothétiques
US10952851B2 (en) Delivery apparatus for self-expanding medical device

Legal Events

Date Code Title Description
17P Request for examination filed

Effective date: 20141118

AC Divisional application: reference to earlier application

Ref document number: 2341871

Country of ref document: EP

Kind code of ref document: P

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO SE SI SK SM TR

PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION IS DEEMED TO BE WITHDRAWN

18D Application deemed to be withdrawn

Effective date: 20150912